Hydrogels and ttfield-generating systems comprising the hydrogel

Abstract

An improved hydrogel configuration for use with a TT electric field generating system is disclosed. A kit containing the improved hydrogel configuration and a method for manufacturing and using the improved hydrogel configuration are also disclosed.

Description

Porous hydrogel configurations, manufacturing methods, and applications Cross-reference to related applications / The declaration is incorporated by reference. This patent application claims priority to the following: U.S. Provisional Patent Application No. 62 / 932,653, filed November 8, 2019, entitled "Conductive Gel Compositions and Methods of Production and Use Thereof"; U.S. Provisional Patent Application No. 62 / 955,563, filed December 31, 2019, entitled "Performed Hydrogel Configurations and Methods of Production and Use Thereof"; and U.S. Provisional Patent Application No. 62 / 955,563, filed January 3, 2020, entitled "Performed Hydrogel Configurations and Methods of Production and Use Thereof". The full contents of U.S. Provisional Patent Application No. 62 / 956,916, entitled "Theoretical Application for the Study of the ... Statement regarding federally funded research or development not applicable. A tumor treating field (TT field or TTF) is a low-intensity (e.g., 1 to 3 V / cm) alternating current electric field in the mid-frequency range (100 to 500 kHz) that targets solid tumors by interfering with mitosis. This non-invasive treatment targeting solid tumors is described, for example, in U.S. Patent Nos. 7,016,725; 7,089,054; 7,333,852; 7,565,205; 8,244,345; 8,715,203; 8,764,675; 10,188,851; and 10,441,776. A TT field is typically delivered via two pairs of transducer arrays that generate a vertical electric field within the treated tumor; the electrode arrays constituting each of these pairs are positioned on opposite sides of the treated body site. More specifically, for OPTUNE... ®The system (Novocure Limited, St. Helier, Jersey) has one pair of electrodes positioned on the left and right sides of the tumor (LR), and another pair of electrodes positioned on the anterior and posterior sides of the tumor (AP). TT fields are approved for the treatment of glioblastoma multiforme (GBM) and can be used, for example, via OPTUNE. ® The system delivery system includes an array of converters placed on the patient's shaved head. OPTUNE ® Each transducer array in the device for delivering the TT electric field comprises a set of ceramic disk electrodes coupled to the patient's skin (such as, but not limited to, the shaved head of a patient treating GBM) via a conductive medical gel layer. The medical gel is designed to deform to conform to the contours of the human body and provide good electrical contact between the array and the skin; thus, the gel interface bridges the skin and reduces interference. The device is intended to be worn continuously by the patient for 2 to 4 days, then removed for hygiene and regrowth (if necessary), followed by reapplication with a new set of arrays. Thus, the medical gel remains in substantially continuous contact with the patient's skin area for 2 to 4 days at a time, with only brief periods of occlusion and exposure to the environment before further application of medical gel. Various types of medical gels are known in the art. One specific type of gel that can be used as part of a TT electric field generating system is a conductive hydrogel. Hydrogels are three-dimensional (3-D) networks of hydrophilic polymers that can swell and hold large amounts of water while maintaining their structure due to the chemical or physical cross-linking of individual polymer chains. Hydrogels are used in many fields, including medicine, where they are non-toxic and biocompatible. (Bahram et al. (2016) "An Introduction to Hydrogels and Some Recent Applications.") Emerging Concepts in Analysis and Applications of Hydrogels . InTech Open). However, in Phase III trials and post-market surveillance programs, dermatologic adverse events (dAEs) were observed with existing medical-grade hydrogels and TT electric field generation systems, with incidence rates of 16% and 22%, respectively. These dAEs included (but were not limited to) allergic and irritant dermatitis, dissociation, mechanical injury, ulceration, and skin infection. Specifically, irritant contact dermatitis and allergic contact dermatitis could be caused by chemical irritation from the hydrogel and allergy to the hydrogel, respectively. Skin dissociation caused by prolonged exposure to the hydrogel could lead to lesions / ulcers on the skin, which were subsequently susceptible to infection. Because the hydrogel requires continuous contact with the patient's skin for several days at a time, while there is no extended "breathing" period between applications of the TT electric field array to the skin, these adverse events are more severe. (Lacouture et al. (2014)) Seminars in Oncology, 41:S1-S14). Currently available medical hydrogels are typically too acidic for prolonged wear, thus damaging the skin after extended exposure. Additionally, the bottom liner adhesion (i.e., skin adhesion) of currently available hydrogels is typically insufficient to provide the necessary level of skin adhesion for the required wear time. Furthermore, adjusting either of these properties can increase the hydrogel's resistivity, thereby affecting its ability to conduct current. Additionally, when the hydrogel comes into contact with sweat during wear, it swells and degrades, further increasing resistivity. Moreover, over approximately three days of wear, the loss of the hydrogel interface (such as (but not limited to) erosion of the hydrogel's adhesiveness and conductivity) reduces the standard current / field generated by the TT electric field system, thus diminishing the functionality and overall effectiveness of TT electric field therapy. For a further discussion of the general properties of hydrogels, please refer to Okay, Oguz. (1970). General Properties of Hydrogels. 10.1007 / 978-3-540-75645-3_1. Due to the prolonged exposure and the unique use of the hydrogel in conjunction with the TT electric field system, novel and improved conductive hydrogel configurations with a variety of unique properties that differ from those typically found in currently available medical-grade hydrogels are required. This document discloses such conductive hydrogel configurations, kits containing them, and methods for their manufacture and use. Before explaining in detail at least one embodiment of the concept of the present invention (one or more) with the aid of illustrative language and results, it should be understood that the concept of the present invention (one or more) in its application is not limited to the details of the construction and configuration of the components set forth in the following description. The concept of the present invention (one or more) can have other embodiments or can be practiced or implemented in various ways. Therefore, the language used herein is intended to be given the broadest possible scope and meaning; and the embodiments are intended to be illustrative and not exhaustive. Furthermore, it should be understood that the idioms and terms used herein are for descriptive purposes and should not be considered limiting. Unless otherwise defined herein, scientific and technical terms used in connection with the concepts of the invention(s) disclosed herein shall have the meanings commonly understood by one of ordinary skill in the art. Furthermore, unless the context otherwise requires, singular terms shall include plural terms and plural terms shall include singular terms. The foregoing techniques and procedures are generally performed according to well-known methods in the art and as described in the various general and more specific references cited and discussed throughout this specification. The nomenclature and laboratory procedures and techniques used herein in conjunction with analytical chemistry, synthetic organic chemistry, and pharmaceutical and pharmaceutical chemistry are well-known and commonly used in the art. Standard techniques are used for chemical synthesis and chemical analysis. All patents, published patent applications, and non-patent publications mentioned in this specification indicate the level of skill of those familiar with (one or more) the technical field to which the inventive concepts disclosed herein pertain. All patents and published patent applications mentioned in any part of this application are expressly incorporated herein by reference in their entirety as if each individual patent or publication were specifically and individually indicated to be incorporated herein by reference. All components, kits, and / or methods disclosed herein can be prepared and performed without excessive experimentation based on the disclosure herein. While components, kits, and methods of the present invention have been described according to specific embodiments, it will be apparent to those skilled in the art that variations may be applied to the components and / or methods and steps or sequences of steps described herein without departing from the concept, spirit, and scope of the present invention. It will be apparent to those skilled in the art that all such similar substitutions and modifications should be considered to fall within the spirit, scope, and concept of the present invention as defined in the appended claims. As used in accordance with the disclosure herein, unless otherwise indicated, the following terms shall be understood to have the following meanings: When used in conjunction with the term "comprising" in the claims and / or this specification, the term "a / an" may mean "one," but it also corresponds to "one or more," "at least one," and "one or more." Therefore, unless expressly indicated otherwise in the context, the terms "a / an" and "the" include a plurality of references. Thus, for example, reference to "a compound" may refer to one or more compounds, two or more compounds, three or more compounds, four or more compounds, or a greater number of compounds. The term "plural" means "two or more." The term "at least one" should be understood to include one and any quantity exceeding one, including but not limited to 2, 3, 4, 5, 10, 15, 20, 30, 40, 50, 100, etc. Depending on the terms attached to it, the term "at least one" can be extended to 100 or 1000 or more; furthermore, the quantity of 100 / 1000 should not be considered limiting, as higher limits can also produce satisfactory results. Additionally, the term "at least one of X, Y, and Z" should be understood to include X alone, Y alone, and Z alone, as well as any combination of X, Y, and Z. The use of ordinal terms (i.e., "first," "second," "third," "fourth," etc.) is solely for the purpose of distinguishing two or more items and does not imply any order or sequence of importance or any order of addition of one item relative to another. Unless explicitly indicated to refer only to options or unless the options are mutually exclusive, the term "or" is used in the scope of a patent application to mean inclusive "and / or". For example, any of the following satisfies the condition "A or B": A is true (or exists) and B is false (or does not exist), A is false (or does not exist) and B is true (or exists), and both A and B are true (or exist). As used herein, any reference to "one embodiment," "an embodiment," "some embodiments," "an example," "for example," or "an embodiment" means that a particular element, feature, structure, or characteristic described in connection with an embodiment is included in at least one embodiment. For example, the phrases "in some embodiments" or "an example" appearing throughout this specification do not necessarily refer to the same embodiment. Furthermore, all references to one or more embodiments or examples should be understood as not being restrictive on the scope of the claims. Throughout this application, the term "about" is used to indicate values ​​including variations in the composition / equipment / apparatus, the inherent error of the method used to determine the value, or variations present in the object of study. For example, but not as a limitation, when using the term "about," a specified value may vary relative to that specified value by positive or negative 20%, or 15%, or 12%, or 11%, or 10%, or 9%, or 8%, or 7%, or 6%, or 5%, or 4%, or 3%, or 2%, or 1%, as such variations are suitable for performing the disclosed method and as understood by one of ordinary skill in the art. As used in this specification and the claims of one or more patent applications, the terms "comprising" (and any form of inclusion, such as "comprise" and "comprises"), "having" (and any form of having, such as "have" and "has"), "including" (and any form of inclusion, such as "includes" and "include"), or "containing" (and any form of containing, such as "contains" and "contain") are inclusive or open-ended and do not exclude other, unlisted elements or method steps. As used herein, the term "or combinations thereof" refers to all permutations and combinations of the items listed preceding the term. For example, "combinations of A, B, C, or the like" is intended to include at least one of the following: A, B, C, AB, AC, BC, or ABC, and, where the order is important in a particular context, also BA, CA, CB, CBA, BCA, ACB, BAC, or CAB. Continuing this example, combinations containing repetitions of one or more items or terms are explicitly included, such as BB, AAA, AAB, BBC, AAABCCCC, CBBAAA, CABABB, etc. Those skilled in the art will understand that, unless otherwise apparent from the context, there is typically no limit to the number of items or terms in any combination. As used herein, the term "substantially" means that the subsequently described event or situation occurs completely or to a great extent. For example, when connected with a particular event or situation, the term "substantially" means that the subsequently described event or situation occurs at least 80% of the time, or at least 85% of the time, or at least 90% of the time, or at least 95% of the time. For example, the term "substantially adjacent" can mean that two items are 100% adjacent to each other, or that two items are closely adjacent to each other but not 100% adjacent, or that a portion of one of two items is not 100% adjacent to the other item but is closely adjacent to it. As used herein, the term "polypeptide" should be understood as a polymer of amino acids. This polymer may include d-, l-, or artificial variants of amino acids. Additionally, the term "polypeptide" should be understood to include peptides, proteins, and glycoproteins. As used herein, the term "polynucleotide" should be understood as a polymer of two or more nucleotides. As used herein, nucleotide should be understood to include deoxyribonucleotides and / or ribonucleotides and their artificial variants. The term polynucleotide also includes single-stranded and double-stranded molecules. As used herein, the terms "analyte" or "variant" should be understood as a variant of the normal or standard form or wild-type form of a molecule. For polypeptides or polynucleotides, analogs may be variants (polymorphisms), mutants, and / or naturally occurring or artificially modified forms of wild-type polynucleotides (including combinations thereof). Such analogs may be more, more complete, less, intermediate, or less active than the normal form of the molecule, or completely inactive. Or and / or, for chemical substances, analogs may be any structure having the desired functional group (including alterations or substitutions in the core moiety), or even containing different atoms or isomeric configurations. As used herein, the phrases “associated with” and “coupled to” include two parts directly associated / joined with each other, and two parts indirectly associated / joined with each other. For example, non-limiting examples of association / coupling include covalently joining one part to another by a direct bond or via a spacer group, non-covalently joining one part to another by means of a specific binding pair member bound to those parts, such as by dissolving one part into another part or by synthesis, and coating one part onto another part. As used herein, "substantially pure" means that the target species is the dominant species (i.e., more abundant than any other individual species in the composition in moles), and preferably, the substantially purified portion is a composition in which the target species constitutes at least about 50% (in moles) of all macromolecular species present. Generally, a substantially pure composition will contain more than about 80%, more preferably more than about 85%, 90%, 95%, and 99% of all macromolecular species present in the composition. Ideally, the target species is purified to be substantially homogeneous (so that contaminant species cannot be detected in the composition by conventional detection methods), wherein the composition consists essentially of a single macromolecular species. The term "medically acceptable" means compounds and components that are suitable for administration to humans and / or animals without causing undue adverse side effects, such as (but not limited to) toxicity, irritation and / or allergic reactions, in proportion to a reasonable benefit / risk ratio. The term "medically acceptable excipient" means any carrier, mediator, and / or diluent known in the art or otherwise contemplated herein that may improve the solubility, deliverability, dispersibility, stability, and / or configurational integrity of the compositions disclosed herein. As used herein, the term "patient" includes both human and veterinary individuals. For therapeutic purposes, "mammal" means any animal classified as a mammal, including but not limited to humans, domestic and farm animals, non-human primates, and any other animal with mammary tissue. The term "treatment" refers to therapeutic treatment and preventive or preventative measures. Those requiring treatment include, but are not limited to, individuals who already have a specific condition / disease / infection and individuals at risk of developing a specific condition / disease / infection (e.g., individuals requiring preventive / preventative measures). The term "treatment" also refers to the administration of a drug / element / method to a patient for therapeutic and / or preventive / preventative purposes. "Therapeutic composition" or "medicinal composition" means a drug that can be administered into the body to produce therapeutic and / or preventive / protective effects. As used herein, the terms "administration" and "administering" should be understood to include all routes of administration known in the art, including but not limited to oral, topical, percutaneous, non-enteric, subcutaneous, intranasal, mucosal, intramuscular, intraperitoneal, intravitreal, and intravenous routes, and both local and systemic administration are included. Furthermore, the components of the disclosure herein (and / or their administration methods) may be designed to provide delayed, controlled, or sustained release using formulation techniques well-known in the art. Turning now to the concept of (one or more) of the present invention, certain non-limiting embodiments thereof relate to conductive gel compositions comprising a porous configuration for application to a patient’s skin during treatment with a TT electric field generating system. The concepts of the inventions (one or more) disclosed and / or claimed herein include, but are not limited to, conductive gels with porous configurations that can be used in conjunction with any existing conductive gels generally known in the art, provided that such conductive gels have sufficient structural integrity to maintain the perforations or protrusions for a duration sufficient to treat the patient before removal and / or replacement of such conductive gels. In a non-limiting embodiment, conductive gel compositions with porous configurations have, compared to existing gel compositions, at least one of a reduced polymer chain length and an added free salt; the reduction in polymer chain length and the increase in free salt concentration maximize the conductivity of the gel while reducing skin irritation caused by the conductive gel. The perforations (or protrusions) on the surface of the modified conductive gel increase airflow between the patient's skin and the conductive gel, thereby reducing (if not eliminating) dissociation, lesions / ulcers, and dermatitis when a TT electric field is applied to the porous gel, and lowering the operating temperature. Furthermore, by increasing the number of perforations and reducing the surface area of ​​the conductive gel, the adhesion of the gel to the substrate is increased. Some non-limiting embodiments of the disclosure herein relate to a composition comprising a semi-solid, porous conductive gel for application to a patient's skin and for placement between the patient's skin and at least one transducer array that generates an alternating electric field having a frequency in the range of about 50 kHz to about 500 kHz. While the concepts of one or more of the inventions disclosed and / or claimed herein are applicable in certain specific (but non-limiting) embodiments to any conductive gel generally known in the art, porous conductive gels contain free salts incorporated within the gel or as a layer of a multilayer gel (i.e., a bilayer gel). The term "free salt" refers to salt molecules that are not incorporated as part of a polymeric chain structure but are substantially free-floating within the gel and are therefore conductive and thus have reduced impedance, being a source of free ions. Alternatively and / or in certain non-limiting embodiments, the porous conductive gel comprises one or more of the following chemical and structural features / properties: polymer chain length in the range of about 1 nm to about 200 nm; free salt concentration in the range of about 0.1 mM to about 1 M; pH in the range of about 6 to about 8; volume resistivity less than about 100 ohms-inch; and skin adhesion of at least about 100 g / inch. Furthermore, given that the conductive gel components are exposed to the patient's skin for extended periods, the gel should be optimized for use at body temperature (i.e., in the range of approximately 34°C to approximately 40°C). At these temperatures, evaporative cooling is maximized by introducing airflow through perforations into the modified porous conductive gel, thereby allowing for a reduction in operating temperature and a cooling effect on the patient's skin. In certain specific (but not limiting) embodiments, the alternating current field is generated within a target area of ​​the patient. The target area typically contains at least one tumor, and the generation of the alternating current field selectively disrupts or inhibits tumor growth. The alternating current field can be generated at any frequency to selectively disrupt or inhibit tumor growth. For example (but not as a limitation), the frequency of the alternating current electric field can be approximately 50 kHz, approximately 75 kHz, approximately 100 kHz, approximately 125 kHz, approximately 150 kHz, approximately 175 kHz, approximately 200 kHz, approximately 225 kHz, approximately 250 kHz, approximately 275 kHz, approximately 300 kHz, approximately 325 kHz, approximately 350 kHz, approximately 375 kHz, approximately 400 kHz, approximately 425 kHz, approximately 450 kHz, approximately 475 kHz, or approximately 500 kHz, and ranges formed by any of the above values ​​(i.e., the range from approximately 100 kHz to approximately 300 kHz, the range from approximately 100 kHz to approximately 150 kHz, the range from approximately 150 kHz to approximately 300 kHz, etc.), and ranges of two integers falling between two of the values ​​mentioned above (i.e., the range from approximately 32 kHz to approximately 333 kHz, approximately 78 kHz, etc.). (ranging from kHz to approximately 298 kHz, etc.). Although the invention described herein primarily involves alternating current or electric fields (one or more), those skilled in the art will readily recognize that the concepts of the inventions disclosed and / or claimed herein further envision the use of direct current or electric fields (one or more). In certain specific (but not limiting) implementations, an alternating electric field may be applied at two or more different frequencies. When two or more frequencies are present, each frequency is selected from any of the values ​​mentioned above, or a range formed by any of the values ​​mentioned above, or a combination of two integers falling between two of the values ​​mentioned above. As previously mentioned, the conductive gel employed according to the concepts of one or more inventions disclosed and / or claimed herein may comprise any composition generally known in the art and may take any form that allows the gel to function as disclosed herein. For example (but not as a limitation), the conductive gel may be in the form of a hydrogel or hydrocolloid. In some non-limiting embodiments, the conductive gel is a porous conductive polymeric hydrogel. In some non-limiting embodiments, the conductive gel is a porous polysiloxane. In certain specific (but not limiting) embodiments, the gel is sterile. Additionally, in certain non-limiting embodiments, the gel will not substantially degrade upon exposure to sterilization conditions including gamma rays or ethylene oxide gas. The gel may be formed from any hydrophilic polymer that allows the gel to function as disclosed herein. For example (but not as a limitation), the gel may be a polyacrylic acid gel, a provitamin gel, or a cellulose gel. Additionally, the gel may contain at least one of the following: polyglucosamine, alginate, agarose, methylcellulose, hyaluronic acid, collagen, laminin, matrigel, fibronectin, vitronectin, poly-1-lysine, proteoglycans, fibrin glue, gels obtained by engineered and / or decellularized natural tissues, and any combination thereof. In addition, the gel may contain at least one of the following: polyglycolic acid (PGA), polylactic acid (PLA), polycaprolactone (PCL), polyvinyl alcohol (PVA), polyethylene glycol (PEG), methyl methacrylate, poly(methyl methacrylate) (PMMA), poly(2-hydroxyethyl methacrylate) (HEMA), poly(glycerol sebacate), polyurethane, poly(isopropylacrylamide), poly(N-isopropylacrylamide), or any combination thereof. The polymer of the gel may have any polymer chain length that allows the gel composition to function as described herein. For example (but not as a limitation), the polymer chain length may be approximately 1 nm, approximately 2 nm, approximately 3 nm, approximately 4 nm, approximately 5 nm, approximately 6 nm, approximately 7 nm, approximately 8 nm, approximately 9 nm, approximately 10 nm, approximately 15 nm, approximately 20 nm, approximately 25 nm, approximately 30 nm, approximately 35 nm, approximately 40 nm, approximately 45 nm, approximately 50 nm, approximately 55 nm, approximately 60 nm, approximately 65 nm, approximately 70 nm, approximately 75 nm, approximately 80 nm, approximately 85 nm, approximately 90 nm, approximately 95 nm, approximately 100 nm, approximately 105 nm, approximately 110 nm, approximately 115 nm, approximately 120 nm, approximately 125 nm, approximately 130 nm, approximately 135 nm, approximately 140 nm, approximately 145 nm, approximately 150 nm, approximately 155 nm, approximately 160 nm, approximately 165 nm, approximately 170 nm, approximately 175 nm, approximately 180 nm, approximately 185 nm, etc. nm, approximately 190 nm, approximately 195 nm, approximately 200 nm and higher, and ranges combining any two of the values ​​mentioned above (i.e., the range of approximately 3 nm to approximately 175 nm, the range of approximately 5 nm to approximately 150 nm, or the range of approximately 10 nm to approximately 125 nm, the range of approximately 15 nm to approximately 100 nm, etc.), and ranges combining two integers falling between the two values ​​mentioned above (i.e., the range of approximately 3 nm to approximately 157 nm, etc.). In other non-limiting embodiments, the range of polymer chain length depends on the frequency(s) of the alternating current field. For example (but not as a limitation), the range of polymer chain length may be based on the frequency range of the alternating current field. Non-limiting examples include a range of about 5 nm to about 50 nm when the alternating current field has a frequency in the range of about 50 kHz to about 150 kHz; a range of about 50 nm to about 100 nm when the alternating current field has a frequency in the range of about 150 kHz to about 300 kHz, and so on. When present, the free salt present in the conductive gel can be any salt or other substance that serves as a source of free ions capable of substantially floating freely within the conductive gel (i.e., enhancing the ion flow within the conductive gel), wherein such free ions are used for conduction and thus reduce impedance. In certain specific (but not limiting) embodiments, the free salt present in the conductive gel is a source of calcium ions, chloride ions, citrate ions, silver ions, iodide ions, etc., or any other ions known to be good conductors. Non-limiting examples of free salts that can be utilized according to the disclosure herein include those containing potassium (K) or ammonium (NH4+). 4+Sodium (Na) and calcium (Ca) 2+ ), silver (Ag) + Salts of nitrate, bicarbonate, and their analogues. Specific non-limiting examples of free salts that can be utilized according to the disclosure herein are NaCl, KCl, and CaCl. 2. MgCl 2. ZnCl 2. Iodine, silver iodide (AgI), silver chloride (AgCl), silver dihydrogen citrate (SDC), sodium citrate, calcium bicarbonate, combinations thereof, and analogues thereof. When present, free salts present in a conductive gel can have any concentration that allows the gel composition to function as described herein. For example (but not as a limitation), the free salt concentration may be at least about 0.1 mM, about 0.5 mM, about 1 mM, about 2 mM, about 3 mM, about 4 mM, about 5 mM, about 6 mM, about 7 mM, about 8 mM, about 9 mM, about 10 mM, about 15 mM, about 20 mM, about 25 mM, about 30 mM, about 35 mM, about 40 mM, about 45 mM, about 50 mM, about 55 mM, about 60 mM, about 65 mM, about 70 mM, about 75 mM, about 80 mM, about 85 mM, about 90 mM, about 95 mM, about 100 mM, about 150 mM, about 200 mM, about 250 mM, about 300 mM, about 350 mM, about 400 mM, about 450 mM, about 500 mM. mM, approximately 550 mM, approximately 600 mM, approximately 650 mM, approximately 700 mM, approximately 750 mM, approximately 800 mM, approximately 850 mM, approximately 900 mM, approximately 950 mM, approximately 1 M, or higher, and any range combining any two of the values ​​mentioned above (i.e., the range from approximately 0.1 mM to approximately 100 mM, the range from approximately 1 mM to approximately 50 mM, etc.), and the range combining two integers falling between the two values ​​mentioned above (i.e., the range from approximately 12 mM to approximately 550 mM, etc.). In other non-limiting embodiments, the free salt concentration, when present, depends on the frequency(s) of the alternating current field(s). For example (but not as a limitation), the range of free salt concentration may be based on the frequency range of the alternating current field. Non-limiting examples include a range of about 0.1 mM to about 50 mM when the alternating current field has a frequency in the range of about 50 kHz to about 150 kHz; and a range of about 50 mM to about 100 mM when the alternating current field has a frequency in the range of about 150 kHz to about 300 kHz. While the non-limiting embodiments described above disclose that free salts are dispersed in the conductive gel when present, it should also be understood that free salts may also be present in one or more layers that are not conductive gels (or other than conductive gels). For example (but not as a limitation), an additional layer may be located between the patient's skin and the conductive gel, and free salts may be dispersed in this additional layer. Specifically (but not as a limitation), when on the skin, silver chloride separates into silver ions and chloride ions, thereby facilitating ion transfer into the skin and improving recovery rate and sensing capability. The conductive gel may have any pH that does not damage the patient’s skin or cause chemical irritation after prolonged exposure to the gel. For example (but not as a limitation), the pH of the gel may be about 6, about 6.5, about 7, about 7.5, about 8, and any range of the above values ​​(i.e., the range of about 6 to about 8, the range of about 6.5 to about 7.5, etc.). Conductive gels may have any moisture content that allows the gel components to function as described herein and reduces any skin irritation after prolonged exposure to the gel. For example (but not as a limitation), the water concentration of the conductive gel may be less than or equal to about 70%, less than or equal to about 69%, less than or equal to about 68%, less than or equal to about 67%, less than or equal to about 66%, less than or equal to about 65%, less than or equal to about 64%, less than or equal to about 63%, less than or equal to about 62%, less than or equal to about 62%, less than or equal to about 60%, less than or equal to about 59%, less than or equal to about 58%, less than or equal to about 57%, less than or equal to about 56%, less than or equal to about 55%, less than or equal to about 54%, less than or equal to about 53%, less than or equal to about 52%, less than or equal to about 51%, less than or equal to about 50% or lower, and any range of any two of the values ​​mentioned above (i.e., the range of about 50% to about 70%, the range of about 50% to about 60%, the range of about 52% to 58%, etc.). In a particular (but not limiting) embodiment, the pH of the conductive gel is in the range of about 6 to about 8, and the water concentration is in the range of about 50% to about 70%. Conductive gels can possess any level of volume resistivity that maximizes their conductivity. For example (but not as a limitation), the volume resistivity of the conductive gel can be less than about 100 ohms-inch, less than about 95 ohms-inch, less than about 90 ohms-inch, less than about 85 ohms-inch, less than about 80 ohms-inch, less than about 75 ohms-inch, less than about 70 ohms-inch, less than about 65 ohms-inch, less than about 60 ohms-inch, less than about 55 ohms-inch, less than about 50 ohms-inch, less than about 45 ohms-inch, less than about 40 ohms-inch. Less than about 35 ohms-inch, less than about 30 ohms-inch, less than about 25 ohms-inch, less than about 20 ohms-inch, less than about 15 ohms-inch, less than about 10 ohms-inch, or smaller, and any of the above values ​​(i.e., the range from about 10 ohms-inch to about 100 ohms-inch, etc.) and combinations falling between two integers of the values ​​mentioned above (i.e., the range from about 13 ohms-inch to about 96 ohms-inch, etc.). The conductive gel may have any skin adhesion rate that allows it to function as disclosed herein. For example (but not as a limitation), the skin adhesion rate of the conductive gel may be at least about 50 g / inch width, at least about 60 g / inch, at least about 70 g / inch, at least about 80 g / inch, at least about 90 g / inch, at least about 100 g / inch, at least about 110 g / inch, at least about 120 g / inch, at least about 130 g / inch, at least about 140 g / inch, at least about 150 g / inch. grams per inch, at least approximately 160 grams per inch, at least approximately 170 grams per inch, at least approximately 180 grams per inch, at least approximately 190 grams per inch, at least approximately 200 grams per inch, at least approximately 210 grams per inch, at least approximately 220 grams per inch, at least approximately 230 grams per inch, at least approximately 240 grams per inch, at least approximately 250 grams per inch, at least approximately 260 grams per inch, at least approximately 270 grams per inch. At least approximately 280 g / inch, at least approximately 290 g / inch, at least approximately 300 g / inch, at least approximately 325 g / inch, at least approximately 350 g / inch, at least approximately 375 g / inch, at least approximately 400 g / inch, at least approximately 425 g / inch, at least approximately 450 g / inch, at least approximately 475 g / inch, at least approximately 500 g / inch, or higher, and any of the above values. (The range of approximately 80 g / inch to approximately 90 g / inch, approximately 50 g / inch to approximately 140 g / inch, approximately 120 g / inch to approximately 300 g / inch, approximately 130 g / inch to approximately 500 g / inch, etc.), and the range of two integers that fall between the two values ​​mentioned above (i.e., the range of approximately 115 g / inch to approximately 295 g / inch, etc.). The conductive gel may have any thickness that allows it to function as disclosed herein. Non-limiting examples of thicknesses that may be used as disclosed herein include about 1 mil, about 5 mil, about 10 mil, about 15 mil, about 20 mil, about 25 mil, about 30 mil, about 35 mil, about 40 mil, about 45 mil, about 50 mil, about 55 mil, about 60 mil, about 65 mil, about 70 mil, about 75 mil, about 80 mil, about 85 mil, about 90 mil, about 95 mil, about 100 mil, or higher, and ranges combining any two of the values ​​mentioned above (i.e., the range from about 10 mil to about 50 mil, etc.) and ranges combining two integers falling between the values ​​mentioned above (i.e., the range from about 12 mil to about 48 mil, etc.). However, those skilled in the art will readily recognize that conductive gels (e.g., hydrogels) can be of any thickness capable of realizing the concepts of one or more of the inventions disclosed and / or claimed herein, such that the conductive gel does not substantially dry out during treatment. In certain specific (but not limiting) embodiments, the conductive gel has a shelf life of at least about six months. For example (but not as a limitation), the conductive gel has a shelf life of at least about 12 months. In certain specific (but non-limiting) embodiments (see Figure 7), the conductive gel is a multilayer structure comprising: a gauze having a first side and a second side, wherein a gel binding layer is attached to the first side of the gauze, and a gel skin layer is attached to the second side of the gauze. The gel binding layer is designed to contact the transducer array, while the gel skin layer is designed to contact the patient's skin. Both the gel binding layer and the gel skin layer are formed of any of the conductive gels described or contemplated herein, and may be formed of the same or different conductive gels. The gauze may be formed of any material that allows the composition to function according to the disclosure herein; specifically, the material forming the gauze is typically selected to optimize conductivity and minimize the resistance of the composition. A non-limiting example of a material that can form the gauze is spun nylon. In some non-limiting embodiments, the conductive gel includes and / or is composed of at least one perforation extending through the entire multilayer structure. In some non-limiting embodiments, the conductive gel includes at least one male protrusion extending from one side of the gel skin layer that is attached to the patient's skin. Additionally, the composition may further include a removable top liner attached to the gel binding layer to protect the gel binding layer until use, and / or a removable bottom liner attached to the gel skin layer to protect the gel skin layer until use. Furthermore, when the free salt is present in the form of separate layers, the composition may further include a free salt layer located between the gel skin layer and the removable bottom liner. In certain specific (but not limiting) embodiments, the conductive gel may further comprise at least one additive. Any type of additive may be used in accordance with the disclosure herein to enable the conductive gel to function as disclosed herein and to further enhance the conductivity and non-sensitizing properties of the conductive gel. Non-limiting examples of usable additives include at least one of antibacterial agents, vitamins, moisturizers, or any combination thereof, or the like thereof. Some non-limiting embodiments of the disclosure herein relate to a kit that includes any of the gel-containing compositions disclosed or contemplated herein. In certain specific (but not limiting) embodiments, the kit may further include at least one pair of transducer arrays (i.e., transducer arrays that serve as part of a TT electric field generating system), which generate an alternating electric field with frequencies in the range of about 50 kHz to about 500 kHz after the porous gel composition is applied to the patient's skin. For example (but not as a limitation), the kit may include at least about two pairs of transducer arrays, at least about four pairs of transducer arrays, at least about six pairs of transducer arrays, at least about eight pairs of transducer arrays, at least about ten pairs of transducer arrays, at least about 12 pairs of transducer arrays, at least about 14 pairs of transducer arrays, at least about 16 pairs of transducer arrays, at least about 18 pairs of transducer arrays, at least about 20 pairs of transducer arrays, at least about 22 pairs of transducer arrays, at least about 24 pairs of transducer arrays, at least about 26 pairs of transducer arrays, at least about 28 pairs of transducer arrays, at least about 30 pairs of transducer arrays, at least about 32 pairs of transducer arrays, at least about 34 pairs of transducer arrays, and at least about 36 pairs of transducer arrays. The range of converter arrays, including at least about 38 pairs of converter arrays, at least about 40 pairs of converter arrays, at least about 42 pairs of converter arrays, at least about 44 pairs of converter arrays, at least about 46 pairs of converter arrays, at least about 48 pairs of converter arrays, at least about 50 pairs of converter arrays, or more, and the range of converter arrays combining the logarithm of any two of the values ​​mentioned above (i.e., the range of about two pairs of converter arrays to about 50 pairs of converter arrays, the range of about two pairs of converter arrays to about 20 pairs of converter arrays, etc.), and the range of two integers combining the values ​​mentioned above (i.e., the range of about one pair of converter arrays to about 15 pairs of converter arrays, etc.). Examples of converter arrays serving as part of a TT electric field system are known in the art and described, for example (but not limited to): U.S. Patent Nos. 7,016,725, 7,089,054, 7,333,852, 7,565,205, 7,715,921, 8,170,684, 8,244,345, 8,715,203, 8,764,675, 10,188,851, and 10,441,776; and U.S. Patent Application Nos. US 2018 / 0160933, US 2019 / 0117956, US 2019 / 0307781, and US 2019 / 0308016. Therefore, further description is deemed unnecessary. The porous gel composition may be present in the kit in any form permitted by the disclosure herein. For example, but not as a limitation, the porous conductive gel composition may be provided in the form of one or more sheets or rolls. Furthermore, the porous conductive gel composition may be provided individually, in single units / quantities, or in multiple units / quantities within the kit. In addition to the components described in detail above, the kit may further contain one or more other components / agents for performing any of the specific methods described or envisioned herein. For example (but not as a limitation), the kit may additionally include: (i) components for preparing the skin before placing the porous gel composition and transducer array on the skin (i.e., razor, cleaning composition, or wipe / towel, etc.); (ii) components for removing the gel / transducer array; and / or (iii) components for cleaning the skin after removing the gel / transducer array. The nature of these other components / agents will depend on the specific treatment modality and / or the area / organ to be treated, and their identification is entirely within the skill of one of ordinary skill in the art; therefore, further description is deemed unnecessary. In addition, depending on the sterility, cross-reactivity and stability of the components / reagents, the components / reagents in the kit may be in separate containers / compartments, or various components / reagents may be combined in one or more containers / compartments. Additionally, the kit may further include a set of written instructions explaining how to use one or more components of the kit. Kits of this nature can be used in any of the methods described or conceived herein. Some non-limiting embodiments of the disclosure herein relate to a method comprising: (1) applying any porous conductive gel composition disclosed or contemplated herein to a patient's skin; (2) applying at least one pair of transducer arrays to the porous gel composition disposed on the patient's skin; and (3) generating an alternating electric field with a frequency in the range of about 50 kHz to about 500 kHz for a period of time. In certain specific (but not limiting) implementations, step (2) includes applying at least two pairs of converter arrays to a composition of a porous conductive gel disposed on the patient’s skin. In certain specific (but not limiting) embodiments, the alternating current field is generated within a target area of ​​the patient. The target area typically contains at least one tumor, and the generation of the alternating current field selectively disrupts or inhibits tumor growth. The alternating current field can be generated at any frequency to selectively disrupt or inhibit tumor growth. For example (but not as a limitation), the frequency of the alternating current electric field can be approximately 50 kHz, approximately 75 kHz, approximately 100 kHz, approximately 125 kHz, approximately 150 kHz, approximately 175 kHz, approximately 200 kHz, approximately 225 kHz, approximately 250 kHz, approximately 275 kHz, approximately 300 kHz, approximately 325 kHz, approximately 350 kHz, approximately 375 kHz, approximately 400 kHz, approximately 425 kHz, approximately 450 kHz, approximately 475 kHz, or approximately 500 kHz, and ranges formed by any of the above values ​​(i.e., the range from approximately 100 kHz to approximately 300 kHz, the range from approximately 100 kHz to approximately 150 kHz, the range from approximately 150 kHz to approximately 300 kHz, etc.), and ranges of two integers falling between two of the values ​​mentioned above (i.e., the range from approximately 32 kHz to approximately 333 kHz, approximately 78 kHz, etc.). (ranging from kHz to approximately 298 kHz, etc.). In certain specific (but not limiting) implementations, the alternating electric field can be generated at two or more different frequencies. When two or more frequencies are present, each frequency is selected from any of the values ​​mentioned above, or a range formed by any of the values ​​mentioned above, or a combination of two integers falling between two of the values ​​mentioned above. In certain specific (but not limiting) implementations, the components and at least one pair of converter arrays remain on the patient's skin for at least about three days. In certain specific (but not limiting) embodiments, the method includes the following steps: (4) removing at least one pair of transducer arrays and the composition containing porous conductive gel from the patient's skin; (5) preparing the patient's skin for another treatment (such as (but not limited to) cleaning and shaving the skin, if necessary); and (6) repeating steps (1) through (3). Additionally, this cycle of steps (1) through (6) may be repeated multiple times as needed. When steps (1) to (3) are repeated, the composition containing the porous conductive gel and at least one pair of transducer arrays can be placed in a position different from their initial placement; in this way, the repositioned array is treated to minimize any possible dAEs. Referring now to the figures, non-limiting embodiments of various configurations of the porous conductive gel composition disclosed herein are shown. Although the hydrogel is specifically shown in the figures, it will be readily understood by those skilled in the art that the porous (and protruding) configurations disclosed herein can be used with any conductive gel generally known in the art. Referring now to Figure 1, a schematic diagram 10 of a TT electric field generating system 14 constructed according to the concept of one or more inventions disclosed and / or claimed herein is shown. As generally shown in Figure 1, a hydrogel 18 provides an adhesion interface 20 between at least one insulating electrode 22 of the TT electric field generating system 14 and the patient's epidermal layer 26 for delivering at least one TT electric field to and / or through the patient's epidermal layer 26 and / or one or more dermal / subcutaneous layers 30. The insulating electrode 22 is electrically coupled to a wire 34 (also referred to as a conductor), which may include an insulator 38 covering at least a portion of the wire 34. Figure 1 further shows an electronic circuit diagram 50 of the TT electric field generating system 14 constructed according to the concepts of one or more inventions disclosed and / or claimed herein. The electronic circuit diagram 50 includes one or more sections represented by electronic components to illustrate the electrical properties of each element of the TT electric field generating system 14. The electronic circuit diagram 50 generally includes a power source E shown as representing the power supplied via wire 34. he Section 54 is electrically coupled to section 58. Section 58 is described as being connected to capacitor (C). d Resistors connected in parallel (R) d Section 58 represents electrode 22. Section 58 is electrically coupled to a resistor (R). s Section 62 represents hydrogel 18. Section 62 is electrically coupled to a power source (E). seSection 66 represents the adhesion interface 20. Section 66 is electrically coupled to the capacitor (C). e Resistors connected in parallel (R) e Section 70 represents the patient's epidermal layer 26. Section 70 is electrically coupled to a resistor (R). u Section 74 represents (one or more) dermis / subcutaneous layer 30. Figure 2A shows a cross-sectional view of a non-limiting embodiment of a TT electric field generating system 14 constructed according to the concepts disclosed and / or claimed herein (one or more inventions). As shown in Figure 2A, the TT electric field system 14 includes at least one insulating electrode 22 and a porous hydrogel layer 100. The at least one insulating electrode 22 includes at least one non-conductive layer 104, at least one conductive layer 108, and a high-capacitance layer 112 having at least one opening 116 disposed therethrough. Furthermore, as shown in Figure 2A, the porous hydrogel layer 100 includes a top surface 120 and a bottom surface 124, wherein a single central perforation 128 extends through the porous hydrogel layer 100 between the top surface 120 and the bottom surface 124. In one non-limiting embodiment, at least one conductive layer 108 includes at least one conductive element and / or compound and / or is composed of therein, which includes (by way of example only) the element silver. In one non-limiting embodiment, the high capacitance layer 112 comprises and / or is composed of ceramic, and at least one opening 116 contains and / or is coated (e.g., coated on the inner periphery of at least one opening 116) with at least one epoxy resin. The porous hydrogel layer 100 may comprise (one or more) any polymerizable conductive gel as described in more detail elsewhere herein. Although shown in Figures 2A-2B as comprising a single central perforation 128 extending through the porous hydrogel layer 100, it will be readily appreciated by those skilled in the art that the porous hydrogel layer 100 may comprise any number of perforations extending through the porous hydrogel layer 100, capable of realizing (one or more) the concepts disclosed and / or claimed by this invention, including but not limited to: 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 25, 30, 35 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, 100, 125, 150, 175, 200, 225, 250, 275, 300, 325, 350, 375, 400, 425, 450, 500, 525, 550, 575, 600, 625, 650, 675, 700, 725, 750, 775, 800, 825, 850, 875, 900, 925, 950, 975 or greater than or equal to 1,000 perforations. Furthermore, although shown as substantially circular shapes in Figures 2A to 2B (and Figures 3A to 3B, discussed in more detail below), it will be readily understood by those skilled in the art that the perforations (one or more) including the central perforation 128 can be any shape capable of realizing the concepts of the inventions (one or more) disclosed and / or claimed herein, including but not limited to: circles; triangles; squares; rectangles; pentagons; hexagons (shown in more detail in Figure 5); heptagons; octagons; nonagons; decagons; unelectra; dodecagons; asymmetrical shapes such as the numbers 3, 4, 5; dotted stars; plus signs; spirals; or any shape with any number of sides capable of realizing the concepts of the inventions (one or more) disclosed and / or claimed herein. Without being bound by theory, the inventors believe that when filled with air, the perforations including the central perforation 128 can induce an edge effect that focuses the electromagnetic field at the air / hydrogel interface. Therefore, to maximize the edge effect, perforations that maximize the amount of edges forming the air / hydrogel interface can be selected. For this reason, the inventors theoretically believe that perforations with sharp corners can also increase the edge effect. Thus, a hydrogel layer with triangular perforations will have a greater number of sharp corners than a hydrogel layer with circular perforations, and a hydrogel layer with triangular perforations will provide an enhanced electromagnetic field to the patient's body compared to a hydrogel layer with circular perforations. The perforations, including the central perforation 128, may have any size capable of realizing the concepts of the inventions disclosed and / or claimed herein, including but not limited to the size of the distance through a particular perforation being 0.1 mm, 0.2 mm, 0.3 mm, 0.4 mm, 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, or greater than or equal to 3.5 mm. When the porous hydrogel layer 100 contains more than one perforation, the perforations may have the same or different sizes. The perforations, including the central perforation 128, can be formed in and through the porous hydrogel layer 100 by any technique capable of realizing the concepts of the inventions disclosed and / or claimed herein, including but not limited to dye shearing and / or laser cutting techniques. The formation of perforations in and through the porous hydrogel layer can be achieved by one or more automated or non-automated methods. In the non-limiting embodiments shown in Figures 2A and 2B, approximately 90% of the porous hydrogel layer 100 adheres to the patient's epidermal layer 26, while the single central perforation 128 comprises approximately 10% of the porous hydrogel layer 100. As can be seen in Table 1A below, a first test shows that the porous hydrogel layer 100, including the single central perforation 128, introduces air through the single central perforation 128 under the high capacitance layer 112, resulting in a 60% increase in conductivity and a decrease in operating temperature from 40°C to 37.2°C compared to the exemplary non-porous hydrogel. Furthermore, as shown in Table 1B below, a second test shows that the porous hydrogel layer 100, including the single central perforation 128, introduces air through the single central perforation 128 under the high capacitance layer 112, resulting in a 105% increase in conductivity and a decrease in operating temperature from 39.6°C to 38.1°C compared to the exemplary non-porous hydrogel. Table 1A: Comparison of non-porous hydrogel with porous hydrogel layer 100 shown in Figures 2A to 2B (Test 1) Table 1B: Comparison of non-porous hydrogel with porous hydrogel layer 100 shown in Figures 2A to 2B (Test 2) Referring now to Figure 3A, a cross-sectional view is shown of a non-limiting embodiment of a TT electric field generating system 150 constructed according to the concepts of one or more inventions disclosed and / or claimed herein. The insulating electrode 22 of the TT electric field generating system 150 is identical in construction and description to those elements of the TT electric field generating system 14 as described with reference to Figures 2A to 2B. This insulating electrode comprises at least one non-conductive layer 104, at least one conductive layer 108, and a high-capacitance layer 112 having at least one opening 116 disposed therethrough. Therefore, further description is deemed unnecessary. The TT electric field generating system 150 includes a second porous hydrogel layer 154, which includes a top surface 158 and a bottom surface 162, wherein a plurality of perforations 166a-j extend through the second porous hydrogel layer 154 from the top surface 158 to the bottom surface 162. In the non-limiting embodiment shown in Figures 3A to 3B, approximately 50% of the second porous hydrogel layer 154 adheres to the patient's epidermal layer 26, and approximately 50% of the second porous hydrogel layer 154 includes the plurality of perforations 166a-j. As can be seen in Table 2 below, compared with the exemplary non-porous hydrogel, the introduction of increased air through the plurality of perforations 166a-j in the second porous hydrogel layer 154 under the high capacitance layer 112 results in a 14% increase in conductivity and a decrease in operating temperature from 36.6°C to 34°C. Table 2: Comparison of non-porous hydrogel with the second porous hydrogel layer 154 shown in Figures 3A to 3B Referring now to Figure 4A, a cross-sectional view is shown of a non-limiting embodiment of a TT electric field generating system 200 constructed according to the concepts of one or more inventions disclosed and / or claimed herein. At least one electrode 22 of the TT electric field generating system 200 is identical in construction and description to elements of the TT electric field generating system 14 as described with reference to Figures 2A to 2B, and this at least one electrode comprises at least one non-conductive layer 104, at least one conductive layer 108, and a high-capacitance layer 112 having at least one opening 116 disposed therethrough. Therefore, further description is deemed unnecessary. In this non-limiting embodiment, the hydrogel layer 204 includes at least one protrusion 216a-g substantially adhered to the top surface 208 and bottom surface 212 of the high-capacitance layer 112 and extending from the bottom surface 212 of the hydrogel layer 204. The at least one protrusion 216a-g engages and adheres to the patient's epidermal layer 26, while introducing air pockets due to the spacing between the at least one protrusion 216a-g. The number of protrusions 216a-g present on the bottom surface 212 of the hydrogel layer 204 may be any number of protrusions 216a-g capable of realizing the concept of one or more inventions disclosed and / or claimed herein, including but not limited to: 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 8 0, 85, 90, 95, 100, 125, 150, 175, 200, 225, 250, 275, 300, 325, 350, 375, 400, 425, 450, 500, 525, 550, 575, 600, 625, 650, 675, 700, 725, 750, 775, 800, 825, 850, 875, 900, 925, 950, 975, or more than or equal to 1,000 protrusions. Each protrusion 216a-g may be of any shape capable of realizing the concepts of (one or more) of the present invention disclosed and / or claimed. Additionally, each protrusion 216a-g may have the same shape as, a different shape from, and / or have the same or different dimensions as, one or more other protrusions 216a-g. In a non-limiting embodiment, each protrusion 216a-g may have any height (i.e., the distance from the bottom surface 212 to the patient's epidermal layer 26) capable of realizing the concepts of the inventions disclosed and / or claimed herein, including but not limited to: about 0.1 mm, about 0.2 mm, about 0.3 mm, about 0.4 mm, about 0.5 mm, about 0.6 mm, about 0.7 mm, about 0.8 mm, about 0.9 mm, about 1.0 mm, about 1.1 mm, and about 1.2 mm. Heights of approximately 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, or greater than or equal to approximately 3.5 mm. In one non-limiting embodiment, each protrusion 216a-g may be of any diameter capable of realizing the concept of one or more of the inventions disclosed and / or claimed herein, including but not limited to: about 0.1 mm, about 0.2 mm, about 0.3 mm, about 0.4 mm, about 0.5 mm, about 0.6 mm, about 0.7 mm, about 0.8 mm, about 0.9 mm, about 1.0 mm, about 1.1 mm, about 1.2 mm, about 1.3 mm, about 1 mm. Diameters of approximately 4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, or greater than or equal to approximately 3.5 mm. When the hydrogel layer 204 includes more than one protrusion 216, the protrusions 216a-g may have the same or different sizes. In a non-limiting embodiment, each or all of one or more protrusions 216a-g may be conical, wherein the diameter of a portion of a particular protrusion 216 formed on the bottom surface 212 may be larger than a portion of that particular protrusion 216 that contacts the patient's epidermal layer 26. Similarly, the diameter of a portion of a particular protrusion 216 formed on the bottom surface 212 may be smaller than that portion of the particular protrusion 216 that contacts the patient's epidermal layer 26. In the non-limiting embodiments shown in Figures 4A to 4B, approximately 50% of the hydrogel layer 204 adheres to the patient's epidermal layer 26, and at least one protrusion 216a-g comprises approximately 50% of the hydrogel layer 204. Referring now to Figure 5, an illustration shows an exemplary embodiment of a third porous hydrogel layer 240 comprising a hydrogel portion 244 and a plurality of perforations 248. For simplicity, only two perforations 248 are labeled in Figure 5. Except that the plurality of perforations 248 have a hexagonal shape, the third porous hydrogel layer 240 is generally constructed according to the second porous hydrogel layer 154 described in more detail above. Referring now to Figures 6A to 6C, non-limiting embodiments and configurations of porous hydrogel layers constructed according to the disclosure herein are shown. Figure 6A shows a hydrogel layer 260 comprising one or more channels 264 formed within hydrogel 268. Figure 6B shows a hydrogel layer 280 comprising one or more channels 284 formed within hydrogel 288 and a plurality of perforations 292 constructed according to the perforations 166a-j described in more detail above. Figure 6C shows a hydrogel layer 300 comprising one or more channels 304a-c formed within hydrogel 308. As can be seen in these figures, the porous hydrogel layer may comprise a plurality of air channels 264, 684, 304a-c (Figures 6A and 6C) and / or a combination of a plurality of channels 284 and perforations 292 (Figure 6B). Each of channels 264, 284, 304a-c and perforation 292 allows air to be introduced and flow beneath the respective hydrogel layers 260, 280, 300, thereby enabling the benefits of the concepts of one or more inventions disclosed and / or claimed herein, as described elsewhere herein. The hydrogel layers are not limited to the air channel and / or perforation configurations shown in Figures 6A-C. In other embodiments, the hydrogel layers may have other configurations or combinations of air channels and / or perforations, such as nonlinear air channels and / or perforations extending through one or more air channels. Referring now to Figure 7, an exploded view of an exemplary embodiment of the conductive gel 350 is shown. As shown, the conductive gel 350 has a multilayer structure, comprising at least a gauze layer 354 having a first side 358 and a second side 362, a gel binding layer 366 attached to the first side 358 of the gauze layer 354, and a gel skin layer 370 attached to the second side 362 of the gauze layer 354. The gel binding layer 366 is designed to contact at least one insulating electrode 22 of the TT electric field generating system 14, while the gel skin layer 370 is designed to contact the patient's skin, such as the epidermis 26. The gel binding layer 366 and the gel skin layer 370 are each formed from any conductive gel described or contemplated herein, and may be formed from the same or different conductive gels. In one embodiment, the gauze layer 354 may be formed of any material that allows the composition to function according to the disclosure herein; specifically, the material forming the gauze layer 354 is typically selected to optimize conductivity and minimize the resistance of the composition. Non-limiting examples of materials that can form the gauze layer 354 are spun nylon. In some non-limiting embodiments, the conductive gel 350 includes and / or is composed of at least one perforation (e.g., perforation 374) extending through the entire multilayer structure of the conductive gel 530, i.e., each perforation 374 may extend through at least the gel binding layer 366, the gauze layer 354, and the gel skin layer 370. In some non-limiting embodiments, the conductive gel 350 includes at least one protrusion 216 (e.g., protrusion 216h) extending from a first side 378 of the gel skin layer 370 adhering to the patient's skin 26. In one embodiment, the gel skin layer 370 of the conductive gel 350 may be formed according to the hydrogel layers 260, 280 and / or 300 shown in FIG. 6A to C and described in more detail above, such that the gel skin layer 370 includes one or more channels 382 located within the gel skin layer 370 and formed according to one or more channels 264, 284 and / or 304a-c. In one embodiment, the conductive gel 350 includes one or more of the following: at least one perforation 374 extending through at least the gel binding layer 366, the gauze layer 354 and the gel skin layer 370; at least one protrusion 216 extending from a first side 378 of the gel skin layer 370; and at least one channel 382 operable to allow air to be introduced and flow between the first side 378 of the gel skin layer 370 and the patient's epidermal layer 26. Alternative constructions of the converter array may also be used, including, for example, converter arrays using non-disc-shaped dielectric ceramic elements, and converter arrays using non-ceramic dielectric materials positioned over a plurality of flat conductors. Examples of the latter include polymer films disposed over one or more conductive pads on a printed circuit board or over one or more flat sheets of conductive materials (such as metals). Exemplary metals include copper, gold, silver, and aluminum. Converter arrays may also be used where the electrode elements are not capacitively coupled to the patient's body. In this case, each element of the converter array will be implemented using a region of conductive material configured to be placed against the body, or against a conductive gel placed against the body, wherein an insulating dielectric layer is not disposed between the conductive material or conductive gel and the body. Other alternative constructions for implementing the converter array may also be used, provided that they (a) deliver a TT electric field to the body and (b) are located at the locations specified herein. Depending on the circumstances, in any of the embodiments described herein, a layer of conductive gel, such as hydrogel, may be disposed between the converter array and the human body. (One or more) Non-limiting illustrative embodiments of the concept of this invention Illustrative Embodiment 1. A hydrogel comprising: a polymeric conductive hydrogel for application to a patient's skin and for placement between the patient's skin and at least one transducer array, the at least one transducer array generating an alternating electric field having a frequency in the range of about 50 kHz to about 500 kHz, wherein the polymeric conductive hydrogel includes a top surface and a bottom surface, further wherein the polymeric conductive hydrogel includes at least one perforation extending through the polymeric conductive hydrogel from the top surface to the bottom surface. Illustrative Embodiment 2. The hydrogel of Illustrative Embodiment 1, wherein at least one perforation is circular in shape. Illustrative Embodiment 3. The hydrogel of Illustrative Embodiment 2, wherein the diameter of the at least one perforation is about 3.175 mm. Illustrative Embodiment 4. The hydrogel of Illustrative Embodiment 1, wherein the shape of the at least one perforation is hexagonal. Illustrative Embodiment 5. A hydrogel comprising: a polymeric conductive hydrogel for application to a patient's skin and for placement between the patient's skin and at least one transducer array, the at least one transducer array generating an alternating electric field having a frequency in the range of about 50 kHz to about 500 kHz, wherein the polymeric conductive hydrogel includes a top surface and a bottom surface, further wherein the polymeric conductive hydrogel includes at least one protrusion extending from the bottom surface of the polymeric conductive hydrogel. Illustrative Embodiment 6. A hydrogel as described in any one of Illustrative Embodiments 1 to 5, wherein the hydrogel is sterile. Illustrative Embodiment 7. A hydrogel as described in any one of Illustrative Embodiments 1 to 6, wherein the hydrogel is a polyacrylic acid gel, a provitamin gel, or a cellulose gel. Illustrative Embodiment 8. A hydrogel as described in any one of Illustrative Embodiments 1 to 6, wherein the hydrogel comprises at least one of the following: polyglucosamine, alginate, agarose, methylcellulose, hyaluronic acid, collagen, laminin, matrix gel, fibronectin, glass connective tissue, poly-1-lysine, proteoglycan, fibrin gel, gels prepared by engineering and decellularization of natural tissues, and combinations thereof. Illustrative Embodiment 9. A hydrogel as described in Illustrative Embodiment 8, wherein the gel comprises at least one of the following: polyglycolic acid (PGA), polylactic acid (PLA), polycaprolactone (PCL), polyvinyl alcohol (PVA), polyethylene glycol (PEG), methyl methacrylate, poly(methyl methacrylate) (PMMA), poly(2-hydroxyethyl methacrylate) (HEMA), poly(glycerol sebacic acid), polyurethane, poly(isopropylacrylamide), poly(N-isopropylacrylamide), or any combination thereof. Illustrative Embodiment 10. A hydrogel as described in any one of Illustrative Embodiments 1 to 9, wherein the pH of the hydrogel is in the range of about 6.5 to about 7.5. Illustrative Embodiment 11. A hydrogel as described in any one of Illustrative Embodiments 1 to 10, wherein the skin adhesion of the hydrogel is at least about 120 grams per inch. Illustrative Embodiment 12. A hydrogel as described in any one of Illustrative Embodiments 1 to 11, wherein the thickness of the hydrogel is in the range of about 10 mils to about 50 mils. Illustrative Embodiment 13. A hydrogel as described in any one of Illustrative Embodiments 1 to 12, wherein the storage life of the hydrogel is at least about six months. Illustrative Embodiment 14. A TT electric field generating system comprising: at least one insulating electrode, the at least one electrode comprising at least one non-conductive layer, at least one conductive layer and a high-capacitance layer having a top surface and a bottom surface, wherein at least one opening is disposed between the top surface and the bottom surface of the high-capacitance layer, further wherein the at least one electrode generates an alternating electric field having a frequency in the range of about 50 kHz to about 500 kHz; and at least one porous hydrogel, the at least one porous hydrogel comprising a polymeric conductive gel having a top surface and a bottom surface, wherein the top surface of the porous hydrogel is adhered to the bottom surface of the high-capacitance layer and the bottom surface of the porous hydrogel is adhered to a patient's skin, further wherein the porous hydrogel comprises at least one perforation extending through the porous hydrogel from the top surface to the bottom surface. Illustrative Embodiment 15. The TT electric field generating system as described in Illustrative Embodiment 14, wherein the TT electric field generating system is integrated into a converter array. Illustrative Embodiment 16. A converter array as described in Illustrative Embodiment 15, wherein the converter array includes at least two TT electric field generating systems. Illustrative Embodiment 17. A TT electric field generating system as described in any one of Illustrative Embodiments 14 to 16, wherein the pH of the porous hydrogel is in the range of about 6.5 to about 7.5. Illustrative Embodiment 18. A TT electric field generating system as described in any one of Illustrative Embodiments 14 to 17, wherein the at least one porous hydrogel is sterile. Illustrative Embodiment 19. A TT electric field generating system as described in any one of Illustrative Embodiments 14 to 18, wherein the shape of the at least one perforation is circular. Illustrative Embodiment 20. A TT electric field generating system as described in any one of Illustrative Embodiments 14 to 18, wherein the shape of the at least one perforation is hexagonal. Illustrative Embodiment 21. A TT electric field generating system as described in any one of Illustrative Embodiments 14 to 20, wherein the skin adhesion rate of the porous hydrogel is at least about 120 g / inch. Although the accompanying disclosure describes the concept of one or more of the invention in conjunction with the specific experiments, results, and language set forth below, it will be apparent to those skilled in the art that many alternatives, modifications, and variations will be readily apparent. Therefore, it is intended to encompass all such alternatives, modifications, and variations that fall within the spirit and broad scope of the disclosure herein. [Figure 1] is a schematic diagram of an exemplary embodiment of an electrode hydrogel system constructed in accordance with the disclosure herein. [Figure 2A] is a cross-sectional view of an exemplary embodiment of a first TT electric field generating system constructed in accordance with the disclosure herein. [Figure 2B] is an illustration of an exemplary embodiment of the first hydrogel layer depicted in Figure 2A. [Figure 3A] is a cross-sectional view of an exemplary embodiment of the second TT electric field generating system constructed in accordance with the disclosure herein. [Figure 3B] is an illustration of the second hydrogel layer depicted in Figure 3A. [Figure 4A] is a cross-sectional view of an exemplary embodiment of a third TT electric field generating system constructed in accordance with the disclosure herein. [Figure 4B] is a diagram of the third hydrogel layer depicted in Figure 4A. [Figure 5] is an illustration of an exemplary embodiment of the fourth hydrogel layer constructed according to the disclosure herein. [Figure 6A] is an illustration of an exemplary embodiment of the fifth hydrogel layer constructed according to the disclosure herein. [Figure 6B] is an illustration of an exemplary embodiment of the sixth hydrogel layer constructed according to the disclosure herein. [Figure 6C] is an illustration of an exemplary embodiment of a seventh hydrogel layer constructed in accordance with the disclosure herein. [Figure 7] is an exploded view of an exemplary embodiment of a conductive gel constructed according to the disclosure herein. 10: Schematic diagram 14: TT Electric Field Generation System 18: Hydrogel 20: Adhesive Interface 22: Insulating electrode 26: Epidermis 30: Dermal / Subcutaneous layer 34: Wires / Conduits 38: Insulator 50: Electronic Circuit Diagram 54: Section 58: Section 62: Section 66: Section 70: Section 74: Section C d Capacitor C e Capacitor E hc :power supply E se :power supply R d Resistor R e Resistor R s Resistor R u Resistor

Claims

1. A hydrogel comprising: a polymeric conductive hydrogel layer for application to a patient's skin and for placement between the patient's skin and at least one transducer array, the at least one transducer array generating an alternating electric field having a frequency in the range of 50 kHz to 500 kHz, wherein the polymeric conductive hydrogel layer includes a top surface and a bottom surface, further wherein the polymeric conductive hydrogel layer includes at least one air-filled perforation extending through the polymeric conductive hydrogel layer from the top surface to the bottom surface.

2. The hydrogel of claim 1, wherein at least one air-filled perforation is circular in shape.

3. The hydrogel of claim 2, wherein the diameter of the at least one air-filled perforation is about 3.2 mm, wherein the term "about" means plus or minus 0.64 mm.

4. The hydrogel of claim 1, wherein the shape of the at least one air-filled perforation is hexagonal.

5. A hydrogel comprising: a polymeric conductive hydrogel layer for application to a patient's skin and for placement between the patient's skin and at least one transducer array, the at least one transducer array generating an alternating electric field having a frequency in the range of 50 kHz to 500 kHz, wherein the polymeric conductive hydrogel layer includes a top surface and a bottom surface, further wherein the polymeric conductive hydrogel layer includes at least one protrusion extending from the bottom surface of the polymeric conductive hydrogel layer.

6. The hydrogel of any one of the requests 1 to 5, wherein the hydrogel is sterile.

7. The hydrogel of any one of claims 1 to 5, wherein the hydrogel is a polyacrylic acid gel, a provitamin gel, or a cellulose gel.

8. A hydrogel as claimed in any one of claims 1 to 5, wherein the hydrogel comprises at least one of the following: polyglucosamine, alginate, agarose, methylcellulose, hyaluronic acid, collagen, laminin, matrix gel, fibronectin, vitronectin, poly-1-lysine, proteoglycan, fibrin gel, gels prepared by engineering and decellularization of natural tissues, and combinations thereof.

9. The hydrogel of claim 8, wherein the hydrogel comprises at least one of the following: polyglycolic acid (PGA), polylactic acid (PLA), polycaprolactone (PCL), polyvinyl alcohol (PVA), polyethylene glycol (PEG), methyl methacrylate, poly(methyl methacrylate) (PMMA), poly(2-hydroxyethyl methacrylate) (HEMA), poly(glycerol sebacic acid), polyurethane, poly(isopropylacrylamide), poly(N-isopropylacrylamide), or any combination thereof.

10. A hydrogel as claimed in any one of claims 1 to 5, wherein the pH of the hydrogel is in the range of 6.5 to 7.

5.

11. The hydrogel of any one of claims 1 to 5, wherein the skin adhesion of the hydrogel is at least 120 g / inch.

12. The hydrogel of any one of claims 1 to 5, wherein the thickness of the hydrogel is in the range of 10 mils to 50 mils.

13. The hydrogel of any one of claims 1 to 5, wherein the storage life of the hydrogel is at least six months.

14. The hydrogel of claim 1, wherein the polymeric conductive hydrogel layer comprises a plurality of air-filled perforations.

15. A TT electric field generating system comprising: at least one insulating electrode, the at least one electrode comprising at least one non-conductive layer, at least one conductive layer and a high-capacitance layer having a top surface and a bottom surface, wherein at least one opening is disposed between the top surface and the bottom surface of the high-capacitance layer, further wherein the at least one electrode generates an alternating electric field having a frequency in the range of 50 kHz to 500 kHz; and at least one hydrogel as claimed in any one of claims 1 to 14.

16. The TT electric field generating system of claim 15, wherein the TT electric field generating system is integrated into a converter array.

17. The TT electric field generating system of claim 16, wherein the at least one insulating electrode comprises two insulating electrodes; and wherein the at least one hydrogel comprises two hydrogels.

18. The TT electric field generating system of any one of claims 15 to 17, wherein the at least one hydrogel is the hydrogel of claim 1, further wherein at least one of the at least one opening disposed between the top and bottom surfaces of the high capacitance layer is aligned with at least one of the at least one air-filled perforation extending from the top surface to the bottom surface through the polymeric conductive hydrogel layer.

19. The TT electric field generating system of claim 15, wherein the at least one hydrogel is the hydrogel of claim 1, further wherein the polymeric conductive hydrogel layer comprises a plurality of air-filled perforations.

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