Patent Application
20240130898
Clinicians approach wound care through various treatment approaches. One way that clinicians determine the stage of a wound or the regression or progression of wounds is through a surrogate value known as pH. pH is a measure of the decimal logarithm of the reciprocal of the local hydrogen ion activity within a wound or wound exudate. In other words it is an indicator of the acidity or alkalinity of a wound or wound exudate. The impact of pH in wound care has shown that if a wound is inflamed, the pH may be in an acidic level (e.g., pH level is 4-6.5). Increased microbial growth may occur when the pH is within the acidic level. If a wound is chronic, the pH may be in an alkaline level (e.g., pH level is 8.0 or greater). Optimum protease activity and cellular migration may occurs when the pH level is around pH 7. Thus, optimum acute healing may occur when the pH level is around pH 7. Therefore, measuring a pH level at a wound area helps stage or even predict potential wound healing or lack of healing outcomes.
One implementation of the present disclosure is a sensor for measuring a pH level in a wound therapy system for treating multiple zones of a wound that includes a circuit configured to measure a pH level at a wound area. The circuit includes a first electrode and one or more second electrodes. The first electrode is configured with a changeable or variable conductivity that changes according to a hydrogen ion concentration level. The one or more second electrodes are configured with a fixed conductivity that does not change with the hydrogen ion concentration level.
Another implementation of the present disclosure is a wound therapy system having a sensor for measuring a pH level at a wound area. The sensor includes a first electrode and one or more second electrodes. The first electrode is configured with a changeable or variable conductivity that changes according to a hydrogen ion concentration level. The one or more second electrodes are configured with a fixed conductivity that does not change with the hydrogen ion concentration level.
Another implementation of the present disclosure is a method of fabricating a sensor for measuring a pH level at a wound area. The method includes: screen-printing a first electrode at a first end of a substrate; depositing iridium oxide on the first electrode; depositing porous protective membrane coating on the first electrode; and screen-printing one or more second electrode at the first end of the substrate. The first electrode has changeable or variable conductivity that changes according to a hydrogen ion concentration level. The one or more second electrodes has fixed conductivity that does not change according to a hydrogen ion concentration level.
Various objects, aspects, features, and advantages of the disclosure will become more apparent and better understood by referring to the detailed description taken in conjunction with the accompanying drawings, in which like reference characters identify corresponding elements throughout. In the drawings, like reference numbers generally indicate identical, functionally similar, and/or structurally similar elements.
Referring to
The first electrode 102 is screen-printed on a first end of the substrate 112. The first end of the substrate 112 is disposed at a wound area to contact with wound fluid when the sensor 100 is in use for a wound therapy system. The first electrode 102 is used for directly contacting wound fluid at the wound area. The first electrode 102 is printed with a carbon-based ink or paste. In some embodiments, the first electrode 102 may be printed using any suitable materials. The first electrode 102 has a circular shape with a predetermined diameter (e.g., approximately lmm) according to some embodiments.
The first electrode 102 is formed with metal oxide electrodeposition of iridium oxide on top of the carbon-based ink or paste. The metal oxide electrodeposition of iridium oxide enables the first electrode 102 with a changeable conductivity according to a hydrogen ion concentration. Measuring the changed conductivity of the first electrode 102 can be used for indicating a change of pH level. When the hydrogen ion concentration at the first electrode 102 increases, the pH level decreases and the conductivity of the first electrode 102 increases. When the hydrogen ion concentration at the first electrode 102 decreases, the pH level increases and the conductivity of the first electrode 102 decreases. In some embodiments, the first electrode 102 can be deposited with any suitable material that allows the conductivity of the first electrode 102 change along with a hydrogen ion concentration level. In some applications, it is believed that direct contact between the wound fluid and the iridium oxide material of the electrode may inhibit the proper operation of the electrode. It would be desirable to provide a coating layer on the electrode that permits ion passage from the wound fluid to the electrode for proper pH determination, while preventing direct contact between the fluid and the electrode in order to protect the electrode.
According to the illustrated embodiment, the first electrode 102 is coated with a porous protective membrane coating to protect the first electrode 102 from the protein rich, enzyme rich, and/or oxidizing wound environments. In some embodiments, the porous protective membrane coating includes a sulfonated and/or carboxylated copolymer, such as a sulfonated tetrafluoroethylene based fluoropolymer-copolymer. A particular example of a sulfonated and/or carboxylated copolymer suitable for the present technology is a copolymer of tetrafluoroethylene with 2-[1-[difluoro-[(trifluoroethenyl)oxy]methyl]-1,2,2,2-tetrafluoroethoxy]-1,1,2,2,-tetrafluoro-ethanesulfonyl fluoride (also referred to as tetrafluoroethylene-perfluoro-3,6-dioxa-4-methyl-7-octenesulfonic acid copolymer). Suitable a sulfonated and/or carboxylated copolymers may be commercially obtained from a variety of sources, and includes (but is not limited to) copolymers utilized for ion exchange membranes and products under the tradename Nafion®. The porous protective membrane is intended to protect the electrode from the deleterious effects of the wound environment, while remaining sufficiently porous to permit ion transfer for determining pH of the wound fluid. According to one embodiment, the porous protective membrane coating comprises a layer of sulfonated and/or carboxylated copolymer disposed over the iridium oxide layer of the electrode. The layer of sulfonated and/or carboxylated copolymer may be formed on the electrode by depositing a solution of the sulfonated and/or carboxylated copolymer on the electrode, where such solutions further include one or more solvents. Such solvents include an organic solvent, water, or both. Exemplary organic solvents include dimethyl ether, diethyl ether, methylene chloride, chloroform, acetone, ethyl acetate, or a combination of any two or more thereof. By way of example of such depositing, an aqueous solution including 5% by weight of tetrafluoroethylene-perfluoro-3,6-dioxa-4-methyl-7-octenesulfonic acid copolymer may be applied to the iridium oxide layer and thereafter the solvent of the aqueous solution removed (e.g., by evaporation). The layer may therefore be formed from solutions including a sulfonated and/or carboxylated copolymer where the sulfonated and/or carboxylated copolymer is included in a concentration, for example, within a range from 5% to 4% by weight of the solution, or within a range from 4% to 3% by weight of the solution, or within a range from 3% to 2% by weight of the solution, or within a range from 2% to 1% by weight of the solution, or within a range from 5% to 6% by weight of the solution, or within a range from 6% to 7% by weight of the solution, or within a range from 7% to 8% by weight of the solution, or within a range from 8% to 9% by weight of the solution, all of which are included within the scope of this disclosure. In some embodiments, the porous protective membrane coating specifically excludes certain materials, such as chitosan, in any concentration, and more particularly excludes chitosan in a concentration of 0.1%-2.5%.
The second electrode 104 is screen-printed on the first end of the substrate 112. In some embodiments, the second electrode 104 includes one or more electrodes. The second electrode 104 is used as a reference electrode with a fixed conductivity. The fixed conductivity of the second electrode 104 does not change along with a change of a hydrogen ion concentration level or a change of pH level. The second electrode 104 is printed with silver chloride paste or ink to provide a better conductivity compared to the first electrode 102. In some embodiments, the second electrode 104 can be printed with any suitable material that allows the second electrode 104 have a fixed conductivity. The second electrode 104 is formed with a shape that is intended to at least partially surround the first electrode 102. The second electrode 104 is disposed in proximity to the first electrode 102.
The third electrode 106 is screen-printed on a second end of the substrate 112. The second end of the substrate 112 is an opposite end to the first end of the substrate 112. In some embodiments, the second end of the substrate 112 does not contact with wound fluid. The third electrode 106 is printed with silver chloride paste or ink. In some embodiments, the third electrode 106 can be printed with any suitable material that allows the third electrode 106 to have a fixed conductivity. The third electrode 106 is used as an electrical contact for voltage measurement. The third electrode 106 is electrically connected to the first electrode 102 via a first electrical trace (not shown).
The fourth electrode 108 is screen-printed on the second end of the substrate 112. In some embodiments, the fourth electrode 108 may include one or more electrodes. The fourth electrode 108 is printed with silver chloride paste or ink. In some embodiments, the fourth electrode 108 can be printed with any suitable material that allows the fourth electrode 108 to have a fixed conductivity. The fourth electrode 108 is used as an electrical contact for voltage measurement. The fourth electrode 106 is electrically connected to the second electrode 104 via a second electrical trace (not shown).
The substrate 112 is made of any suitable material that is bendable, non-stretchable, resistant to tensile and compressive forces, resistant to chemical degradation, and resistant to rapid oxidation. In some embodiments, the substrate 112 is made of polymeric material (e.g., 125 um polymeric film). In some embodiments, the first, second, third, and fourth electrodes 102, 104, 106, and 108 are all printed on the same side of the substrate 112.
The first end of the substrate 112 includes a sealing portion 110 that is formed on the periphery of the first end of the substrate 112. The sealing portion 110 is made of any suitable adhesive material that can seal the first end of the substrate to one or more components of the wound therapy system (e.g., a wound healing pad).
The substrate 112 is coated with an isolation ink layer 114 that separates and protects the printed electrodes (e.g., first, second, third, and fourth electrodes). The isolation ink layer 114 is applied such that only the first electrode 102 and the second electrode 104 are exposed to the wound fluid. In some embodiments, the isolation ink layer 114 includes a cyan screen printed ink.
Referring to
At step 204, a metal oxide layer (e.g., iridium oxide) is deposited on top of the carbon-based ink or paste of the first electrode. The metal oxide electrodeposition enables the first electrode with a changeable conductivity according to a hydrogen ion concentration. In some embodiments, the first electrode can be deposited with any suitable material that allows the conductivity of the first electrode change along with a hydrogen ion concentration level. The metal oxide layer is dried at a desired temperature.
At step 206, a porous protective membrane coating is deposited on the first electrode. The porous protective membrane coating protects the first electrode from the protein rich, enzyme rich, and/or oxidizing wound environments. The porous protective membrane coating is deposited on top of the iridium oxide layer and is formed from a layer of the sulfonated and/or carboxylated copolymer. An aqueous solution comprising approximately 5% (by weight of the solution) sulfonated and/or carboxylated copolymer is deposited on the electrode and then evaporated to form the protective layer. In other embodiments, the solution deposited on the electrode to form the protective layer may comprise the sulfonated and/or carboxylated copolymer in other concentrations, such as within a range from 5% to 4% by weight of the solution, or within a range from 4% to 3% by weight of the solution, or within a range from 3% to 2% by weight of the solution, or within a range from 2% to 1% by weight of the solution, or within a range from 5% to 6% by weight of the solution, or within a range from 6% to 7% by weight of the solution, or within a range from 7% to 8% by weight of the solution, or within a range from 8% to 9% by weight of the solution, all of which are included within the scope of this disclosure. The porous protective membrane coating according to the present embodiment specifically excludes certain materials, such as chitosan. The sulfonated and/or carboxylated copolymer and water-based solution may be deposited on the iridium layer of the electrode using a controlled deposition process (for example a pipet tip or other suitable deposition device) until the first (i.e. working) electrode is covered. The sulfonated and/or carboxylated copolymer and water-based solution may be allowed to self-level on the first electrode until the solution uniformly covers the working electrode. Once the first electrode is uniformly covered then the solution is allowed cure or dry by evaporation at room temperature (for example approximately 20° C.) under a vent hood. A relatively high airflow at room temperature is intended to allow the coating layer to remain somewhat flexible during the drying process and to minimize or prevent the formation of microcracks or other imperfections that could compromise the sulfonated and/or carboxylated copolymerprotective layer.
At step 208, one or more second electrodes are screen-printed at the first end of the substrate. The one or more second electrodes are printed with a material that allows the one or more second electrodes have a fixed conductivity. The fixed conductivity does not change along with a change of a hydrogen ion concentration level or a change of pH level. The one or more second electrodes are printed with silver chloride paste or ink to provide a better conductivity compared to the first electrode. The one or more second electrodes are formed with a shape that is intended to at least partially surround the first electrode. The one or more second electrodes are disposed in close proximity to the first electrode.
According to any embodiment, the sensor 100 for measuring a pH level at a wound site, as shown and described herein, may be incorporated into a wound therapy system 300 having a wound care dressing 304 for use on a patient. The wound care dressing may 304 include negative pressure wound therapy (NPWT). In a NPWT application, the wound care dressing 304 may include any suitable construction and components intended for treatment of a particular wound type. According to one embodiment, the wound care dressing 304 includes a wound interface or contact layer 314 configured to overlie the wound and periwound area 309 of the patent. The wound interface layer 314 may be formed from a fenestrated film, such as a polyurethane film. A wound fluid manifold layer 310 may be provided above the wound interface layer 314. The manifold layer 310 may be formed from a porous hydrophobic foam material, such as GRANUFOAM™ by KCI Licensing, Inc., which is intended to permit and distribute flow of air and wound fluid or exudate from the wound area 309. An absorbent layer 316 may be provided over the manifold layer 310, and may comprise a superabsorbent polymer (SAP) material. The SAP is constructed of a superabsorbent powder, an acetate and ethylene copolymer, and a fiber material. In some embodiments, the superabsorbent powder is a sodium polyacrylate, such as Favor®-PAC320. In some embodiments, the acetate is a glue vinyl acetate, and the acetate and ethylene copolymer may be Pafra 8667. In some embodiments, the fiber material is a 65% viscose and 35% polyethylene terephthalate (PET) spunlace, such as LIDRO 50 g/m2. A drape layer 312 is disposed above the absorbent layer 316 and is formed from a high MVTR film, such as a thin layer of polyurethane film. One example of a suitable material for the drape layer is the polyurethane film known as ESTANE 5714F.
A negative pressure therapy unit 302, such as a V.A.C.ULTA™ Therapy Unit by KCI Licensing, Inc. may be connected to the wound dressing 304 by suitable tubing 306. The tubing 306 may be connected to the drape layer 312 by a tubing connector pad 308, such as a SENSAT.R.A.C. connector by KCI Licensing, Inc. The sensor 100 for measuring a pH level at a wound site may be coupled at, or proximate to, the tubing connector pad in fluid communication with the wound exudate within the dressing. Sensor 100 may communicate with the therapy unit 302 through suitable wired or wireless communication configurations to provide signals representative of the pH of the wound fluid for readout, display, etc. at the therapy unit. According to other embodiments, sensor 100 may communicate with other suitable devices to provide the desired pH information of the wound fluid, such as meters, monitors, smartphones, etc. According to other embodiments, the wound dressing and NPWT therapy system may include other components, or omit recited components, as needed to suit a particular wound treatment strategy, and the sensor 100 may be disposed at any appropriate location within the dressing to expose the first electrode to the wound fluid to obtain a desired pH indication.
As utilized herein, the terms “approximately,” “about,” “substantially,” and similar terms are intended to have a broad meaning in harmony with the common and accepted usage by those of ordinary skill in the art to which the subject matter of this disclosure pertains. It should be understood by those of skill in the art who review this disclosure that these terms are intended to allow a description of certain features described and claimed without restricting the scope of these features to the precise numerical ranges provided. Accordingly, these terms should be interpreted as indicating that insubstantial or inconsequential modifications or alterations of the subject matter described and claimed are considered to be within the scope of the invention as recited in the appended claims.
It should be noted that the terms “exemplary” and “example” as used herein to describe various embodiments is intended to indicate that such embodiments are possible examples, representations, and/or illustrations of possible embodiments (and such term is not intended to connote that such embodiments are necessarily extraordinary or superlative examples).
The terms “coupled,” “connected,” and the like, as used herein, mean the joining of two members directly or indirectly to one another. Such joining may be stationary (e.g., permanent, etc.) or moveable (e.g., removable, releasable, etc.). Such joining may be achieved with the two members or the two members and any additional intermediate members being integrally formed as a single unitary body with one another or with the two members or the two members and any additional intermediate members being attached to one another.
References herein to the positions of elements (e.g., “first end”, “second end”, “top,” “bottom,” “above,” “below,” “between,” etc.) are merely used to describe the orientation of various elements in the figures. It should be noted that the orientation of various elements may differ according to other exemplary embodiments, and that such variations are intended to be encompassed by the present disclosure.
The construction and arrangement of the systems and methods as shown in the various exemplary embodiments are illustrative only. Although only a few embodiments have been described in detail in this disclosure, many modifications are possible (e.g., variations in sizes, dimensions, structures, shapes and proportions of the various elements, values of parameters, mounting arrangements, use of materials, colors, orientations, etc.). For example, the position of elements may be reversed or otherwise varied and the nature or number of discrete elements or positions may be altered or varied. Accordingly, all such modifications are intended to be included within the scope of the present disclosure. The order or sequence of any process or method steps may be varied or re-sequenced according to alternative embodiments. Other substitutions, modifications, changes, and omissions may be made in the design, operating conditions and arrangement of the exemplary embodiments without departing from the scope of the present disclosure.
This application claims the benefit of priority to U.S. Provisional Application No. 62/923,293, filed on Oct. 18, 2019, which is incorporated herein by reference in its entirety.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/IB2020/059721 | 10/14/2020 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 62923293 | Oct 2019 | US |
