|Publication number||US3845757 A|
|Publication date||5 Nov 1974|
|Filing date||12 Jul 1972|
|Priority date||12 Jul 1972|
|Publication number||US 3845757 A, US 3845757A, US-A-3845757, US3845757 A, US3845757A|
|Original Assignee||Minnesota Mining & Mfg|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (8), Referenced by (93), Classifications (7)|
|External Links: USPTO, USPTO Assignment, Espacenet|
. United States Patent 11 1 128/DIG. 4 5 1111.c1.., A6lb 5/04 158 Field 61 Search 128/21 E, 2.06 E, DIG. 4, 128/416-418, 410,411, 404, 405
Weyer 1 Nov. 5, 1974 [541 BIOMEDICAL MONITORING ELECTRODE 3,610,229 10 1971 Zenkich 128 416 x 3,696,807 10 1972 1  James 5- way", Stlllwate 3,701,346 101972 6t al [ZS/2.1 5 [731 Assignec: Minnesota Mining & Manufacturing Company, Saint Paul, Minn. Primary Examiner--Richard A. Gaudet Assistant Examiner-Lee S. Cohen  Flled' July 1972 Attorney, Agent, or Firm-Alexander, Sell, Steldt & [211 Appl. No: 270,954 1361561111111 4 152 US. Cl. 128/2.1 E, 128/206 E, 128/417, 1 1 ABSTRACT A pregellcd intensive care electrode is formed from two layers of soft, conformable foam material having a rigid plastic supporting layer between the foam layers. A conductive connector is in contact with an opencelled spongy material filled with an electrolyte which l56l References Cited provides means for connecting the electrode to moni- UNITED STATES PATENTS toring devices and measuring the electrical impulses -1,170,459 2/1965 Phipps 61 al 128/206 E from a patients Skin- The biomedical monitoring 916C 3,518,984 7/1970 Mason 128/206 E trOde is held in place on the patients skin by means of 3,545,432 12/1970 Berman 128/D1G. 4 a hypo-allergenic pressure sensitive adhesive. 3,587,565 6/197] Tatoian 1 128/206 E 3,599,629 8 1971 Gordy 128/206 E 5 Claims, 3 Drawing Flgllres YQK WOIEF W 24 48mg 2%$%fi%m,
1 BIOMEDICAL MONITORING ELECTRODE BACKGROUND OF THE INVENTION This invention relates to a biomedical monitoring electrode of the type used to detect electrical signals from the skin of a patient. In another aspect, this invention relates to a medical electrode of the type designed for use over a period of several days such as in the intensive or coronary care facilities. In a still further aspect, this invention relates to medical electrodes designed to be used for several days without interfering with the patients normal activities and without becoming dislodged from this original position. In yet a further aspect, this invention relates to medical electrodes of the pregelled type useful in detecting electrical signals from the skin of the patient.
It is known that the conductor portion of electrodes should be maintained away from the skin of the subject by the electrolyte or an electrolyte-filled pad to obtain an electrical contact having minimal resistance and also to minimize the noise caused by motion of the conductive electrolyte with relation to the patients skin.
Pregelled electrodes have been made of rigid plastic cups wherein a cup containing a sponge filled with electrolyte is held against the skin by an elastic sheet. The elastic sheet is attached to the skin by means of a pressure-sensitive adhesive depressing the rigid cup into the patients skin. These electrodes provide an electrode having a broad area of electrolyte contact with the skin. However, the rigid plastic cup of these electrodes is hard and unyielding and the hard plastic cup is uncomfortable when lain on and may irritate the skin of many patients when the electrode is left in place for extended periods. Also the pregelled pad can move in relation to the patients skin and thus cause some noise and inaccuracies in the measurement. Generally,this hard rigid cup construction requires a larger electrode since the adhesive on the elastic sheet next to the rigid cup is not in contact with the patients skin, making this type of electrode bulky.
Briefly, the electrode of this invention comprises a soft, conformable layer of foam having an'aperture therethrough and having on one side of the foam a layer of hypoallergenic adhesive for securing the electrode of thisinvention to the patients skin. Partially covering the foam on the other side is a hard, rigid disc preferably plastic, which covers the aperture and gives rigidity to the electrode configuration. This rigid plastic disc has a conductive snap which is in contact with an open celled sponge filled with an electrolyte in the aperture of the foam layer. The electrolyte filled sponge serves to conduct the electrical signals from the skin of the patient to the conductivesnap or coating of the electrode which is designed for attachment to an external lead suitable for monitoring the patients bodily functions, e.g. an electrocardiogram. The rigid plastic disc and a portion of the first foam layer can be covered by a second soft conformable foam layer which improves the appearance, serves to protect the patient, medical personnel and their clothing from snagging on the exposed edges of the plastic disc and also helps strengthen the total construction.
A better understanding of the invention may be had by reference to the drawing in which:
FIG. 1 is a side view in section of a biomedical monitoring electrode of this invention;
FIG. 2 is a side view in section of a second embodiment of the electrode of this invention;
FIG. 3 is a perspective view of an electrode in place.
Referring to the accompanying drawing, and initially to FIG. 1, reference No. 10, designates generally an intensive care electrode attached to a patients skin 11 by means of a pressure-sensitive adhesive layer 12. The adhesive 12 adheres a soft foam layer 13 having an aperture 14 to the patients skin. A soft, open-celled sponge pad 16 containing an electrolytic gel or cream iscontained in the cavity formed by the patients skin 11, the soft foam layer 13 and the rigid plastic supporting disc 17 which overlays a portion of the foam layer 13. An electrically conductive, e.g., silver or silver chloride-treated, snap 18 passes through the plastic disc and makes contact with the electrolyte filled sponge 16 providing a low resistance electrical pad for impulses from the patients skin to an external monitoring device which can be attached to the snap connector 19 which projects through an aperture 21 in a second layer of soft foam 22 which covers the disc 17. The layers of foam 13, 22 and the rigid disc 17 are adhesively bonded together by means of adhesive layers 23, 24, said layers also serving to adherently bond the foam layers 13, 22 together at the periphery of the intensive care electrode. Adhesive layer 24 also serves to bondthe electrolyte-filled sponge 16 to rigid disc 17 minimizing motion between the patients skin 11 and the conductive snap 18.
FIG. 2 denotes another embodiment of the intensive care electrode of this invention wherein the soft foam layers 13, 22 areadherently bonded by means of adhesive layers 23, 24 to a molded plastic disc 26 with a plastic knob 27 forming a snap connector, the rigid plastic disc 26 and knob 27 being coated with a continuous, electrically coherent conductive layer 28. There exists a conductive path from the patients skin 11 through the electrolyte-filled gel pad 16 to the snap connector 27 which can be attached to external monitoring means such as an electrocardiogram machine.
In FIG. 3, a disc electrode 10 is shown in place on the skin 11 of a patient. The electrode shown is a circular electrode as shown in section in FIG. 1 and is attached firmly to the patients skin 11 by adhesive layer 12. In use, electrical signals from the skin are amplified and sensed by an apparatus (not shown) connected to the male snap connector 19, by a conductive lead and cooperative snap fastener shown by phantom lines 29.
The foams chosen for the practice of this invention are soft and nonirritating to the human skin when left in place for extended periods of time. It is desirable that the foams chosen to make the biomedical monitoring electrode of this invention be substantially closed-cell foams which are not readily permeable to moisture so as to maintain the electrolyte-filled pad in a moistened condition. Use of an open cell foam can result in the gel pad drying out and becoming nonconductive during extended monitoring, resulting in a loss of electrical signals and erroneous readings. Examples of closed cell foams suitable for use in the electrode of this invention are crosslinked polyethylene, polyethylene modified with ethylene vinyl acetate, polyvinyl chloride, etc. These foams normally have a density of about I to 6 pounds per cubic foot with the preferred range of foams being about 2 to 4 pounds per cubic foot. Other closed cell foams having similar resistance to set and strength will form suitable intensive care electrodes of this invention.
The plastic disc laminated in the electrode of this invention provides a support for the electrical connection to the external monitoring means and also serves to rigidify the electrode to maintain adequate spacing between the electrical conductor and the patients skin.
Examples of plastics having suitable properties are polystyrene, polypropylene, acrylonitrilebutadienestyrene copolymers, or rigid polyvinyl chloride. The plastics useful include those having a Rockwell Hardness of about M65-l00 and which do not react with silver and other conductive metals or the ingredients used in the conventional electrolyte gels presently available. Plastics having these characteristics will maintain their structural ability when perforated with a snap connector as shown in FIG. 1. The rigid disc and snap connector can be injection molded as a unitary body and then treated with silver, silver chloride, or other conductive materials to provide a conductive path around said disc as shown in FIG. 2 without impairing the accuracy and stability of the electrode of this invention. The disc could also be formed of other materials such as metals, or glass which will accept a conductive snap connector and will not react when used in contact with the conductive gel.
The pregelled electrode of this invention is designed for use with sodium chloride-based electrolytes such as those which are commercially available and sold in the form of electrolytic pastes or gels. Examples of such gels are EKG-Sol," Redux, and GE. Jel, although other electrolyte gels and creams can also be used.
The adhesives useful in constructing the intensive electrode of this invention are chosen from those adhesives which are nonirritating to the human skin when left in contact therewith over extended periods of time. Preferable adhesives are the hypoallergenic, acrylatebased adhesives such as those of Ulrich US. Pat. No. Re. 24,906. The adhesive holding the electrode of this invention to the skin surfaces the entire bottom of the electrode with the exception of the sponge filled aperture. Because of the construction of this electrode, the skin and the electrolyte-filled sponge, and the electrolyte-filled sponge and rigid disc are held in intimate contact. Therefore, there is little or no opportunity for the skin to shift in relationship to the electrolyte-filled sponge and conductor producing a low noise electrical connection of little variability.
Example I A coating of acrylate adhesive was applied to a strip of().075-inch thick by 2 inches wide polyethylene foam having a density of 2 pounds per cubic foot (Volara" Type A). The adhesively treated surface of the foam was placed on a silicone release liner and 2-inch squares having a five-eighths-inch diameter hole in the center were cut from the resulting laminate.
A coating of the acrylate adhesive was applied on one side of l-inch diameter polystyrene discs 0.040-inch thick. Brass studs having a silver-silver chloride coating and silver eyelets having a silver chloride coating were attached to the centers of the polystyrene discs with the silver eyelets on the adhesively treated surface.
A 0.025-inch polyethylene foam was treated with adhesive as above and 2-inch square pieces having a onefourth-inch diameter hole in the center were cut from the treated foam.
Electrodes were assembled by placing a polystyrene disc adhesive side down on the untreated surface of a 0.075 inch thick foam square such that the silver-silver chloride eyelet was in the hole formed in the polyethylene foam. Next a 0.025-inch layer of the treated polyethylene foam was placed adhesive side down on top of the polystyrene disc with the coated brass stud protruding through the hole in the foam forming a laminate similar to FIG. 1 but without the gelled pad.
A l/2-inch diameter preform was cut from the laminate concentrically around the center. A five-eighthsinch diameter piece of open celled polyurethane foam having a thickness of three-sixteenths-inch and having a density of about 1.1 pounds per cubic foot was placed into the cavity formed by the polystyrene disc and the 0.075-inch thick polyethylene foam. The foam was adhesively bonded in place by the adhesive on the polystyrene disc. Sodium chloride electrolyte (EKG- SOL) was injected into the foam disc; about 0.3 cubic centimeters of electrolyte being injected into the foam.
The electrodes were then packaged in an airtight container to prevent the electrolyte from drying out.
What is claimed is:
l. A medical monitoring electrode for attachment to external monitoring means, said electrode comprising a soft resilient layer having an aperture therethrough, said layer having on one side thereof a coating of hypoallergenic adhesive for securing said electrode to a patients skin and having within said aperture a spongy, open-celled foam filled with a conductive electrolyte, a rigid plastic disc adhered to said layer opposite said adhesive coating and overlying said aperture, said open-celled foam being adhesively retained within said aperture, and an electrically conductive snap carried by said plastic disc and extending above the top face thereof for connection with an external monitoring means and being in electrical contact with said electrolyte at the opposite face of said disc.
2. The electrode of claim 1 having in addition a layer of foam covering the rigid plastic disc and having an aperture therethrough for the connection of the conductive snap to the external monitor.
3. The electrode of claim' 1, where said electrically conductive snap passes through said plastic disc.
4. The electrode of claim 1, where said snap and said disc are a unitary plastic body and have a conductive layer disposed thereon.
5. The electrode of claim 1 wherein the means for adhesively retaining said open-celled foam within said aperture comprises a coating of adhesive on the undersurface of said disc overlying said aperture.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3170459 *||20 Mar 1962||23 Feb 1965||Kelly Glenn F||Bio-medical instrumentation electrode|
|US3518984 *||12 Oct 1967||7 Jul 1970||Univ Johns Hopkins||Packaged diagnostic electrode device|
|US3545432 *||24 Jul 1967||8 Dec 1970||Gulton Ind Inc||Body electrode assembly|
|US3587565 *||25 Aug 1969||28 Jun 1971||Cardiac Electronics Inc||Disposable electrode|
|US3599629 *||28 Aug 1968||17 Aug 1971||Lexington Instr||Oxidized surface biopotential skin electrode|
|US3610229 *||7 Mar 1969||5 Oct 1971||Zenkich Ilias||Electrocardiograph electrodes with conductive jelly supply means|
|US3696807 *||13 Feb 1970||10 Oct 1972||Mdm Corp||Medical electrode with relatively rigid electrolyte cup|
|US3701346 *||4 Jan 1971||31 Oct 1972||Bionetics Inc||Medical electrode|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3964469 *||21 Apr 1975||22 Jun 1976||Eastprint, Inc.||Disposable electrode|
|US3994302 *||14 Aug 1975||30 Nov 1976||Medtronic, Inc.||Stimulation electrode of ion-exchange material|
|US4029086 *||11 Aug 1975||14 Jun 1977||Consolidated Medical Equipment, Inc.||Electrode arrangement|
|US4040412 *||3 Feb 1976||9 Aug 1977||Sato Takuya R||Bioelectrodes|
|US4051842 *||15 Sep 1975||4 Oct 1977||International Medical Corporation||Electrode and interfacing pad for electrical physiological systems|
|US4079731 *||1 Jul 1976||21 Mar 1978||Cardiolink Electrodes, Ltd.||Medical electrodes|
|US4102331 *||21 Sep 1976||25 Jul 1978||Datascope Corporation||Device for transmitting electrical energy|
|US4161174 *||7 Jul 1978||17 Jul 1979||Mercuri Albert R||Biomedical electrode assembly|
|US4653503 *||23 Nov 1983||31 Mar 1987||R2 Corporation||Physiological electrodes for use with magnetic connector|
|US4742828 *||16 Jun 1987||10 May 1988||Rematra Research, Marketing & Trading Co. S.A.||Disposable electrode for monitoring a patient|
|US4938219 *||17 Oct 1989||3 Jul 1990||Fukuda Denshi Co., Ltd.||Electrocardiographic electrode|
|US5012810 *||22 Jun 1990||7 May 1991||Minnesota Mining And Manufacturing Company||Biomedical electrode construction|
|US5078139 *||6 Jun 1990||7 Jan 1992||Minnesota Mining And Manufacturing Company||Biomedical electrode construction|
|US5402780 *||2 Sep 1993||4 Apr 1995||Faasse, Jr.; Adrian L.||Medical electrode with offset contact stud|
|US6121508 *||29 Dec 1995||19 Sep 2000||3M Innovative Properties Company||Polar, lipophilic pressure-sensitive adhesive compositions and medical devices using same|
|US6280463||26 Aug 1998||28 Aug 2001||Zmd Corporation||Reducing skin damage in use of medical electrodes|
|US6453205||12 Oct 2000||17 Sep 2002||Michael R. Dupelle||Reducing skin damage in use of medical electrodes|
|US6795722 *||17 Jun 2002||21 Sep 2004||Neotech Products, Inc.||Electrode sensor package and application to the skin of a newborn or infant|
|US7658196||25 Apr 2007||9 Feb 2010||Ethicon Endo-Surgery, Inc.||System and method for determining implanted device orientation|
|US7775215||7 Mar 2006||17 Aug 2010||Ethicon Endo-Surgery, Inc.||System and method for determining implanted device positioning and obtaining pressure data|
|US7775966||7 Mar 2006||17 Aug 2010||Ethicon Endo-Surgery, Inc.||Non-invasive pressure measurement in a fluid adjustable restrictive device|
|US7816412||23 Feb 2007||19 Oct 2010||Conmed Corporation||Electrically conductive hydrogels|
|US7844342||7 Feb 2008||30 Nov 2010||Ethicon Endo-Surgery, Inc.||Powering implantable restriction systems using light|
|US7848800 *||11 Oct 2002||7 Dec 2010||Eyegate Pharma S.A.S.||Device for delivering medicines by transpalpebral electrophoresis|
|US7927270||29 Jan 2007||19 Apr 2011||Ethicon Endo-Surgery, Inc.||External mechanical pressure sensor for gastric band pressure measurements|
|US7999023||3 Dec 2004||16 Aug 2011||3M Innovative Properties Company||Process for making pressure sensitive adhesive hydrogels|
|US8016744||7 Mar 2006||13 Sep 2011||Ethicon Endo-Surgery, Inc.||External pressure-based gastric band adjustment system and method|
|US8016745||6 Apr 2006||13 Sep 2011||Ethicon Endo-Surgery, Inc.||Monitoring of a food intake restriction device|
|US8034065||26 Feb 2008||11 Oct 2011||Ethicon Endo-Surgery, Inc.||Controlling pressure in adjustable restriction devices|
|US8057492||12 Feb 2008||15 Nov 2011||Ethicon Endo-Surgery, Inc.||Automatically adjusting band system with MEMS pump|
|US8066629||12 Feb 2007||29 Nov 2011||Ethicon Endo-Surgery, Inc.||Apparatus for adjustment and sensing of gastric band pressure|
|US8100870||14 Dec 2007||24 Jan 2012||Ethicon Endo-Surgery, Inc.||Adjustable height gastric restriction devices and methods|
|US8114345||8 Feb 2008||14 Feb 2012||Ethicon Endo-Surgery, Inc.||System and method of sterilizing an implantable medical device|
|US8116841||12 Sep 2008||14 Feb 2012||Corventis, Inc.||Adherent device with multiple physiological sensors|
|US8142452||27 Dec 2007||27 Mar 2012||Ethicon Endo-Surgery, Inc.||Controlling pressure in adjustable restriction devices|
|US8152710||28 Feb 2008||10 Apr 2012||Ethicon Endo-Surgery, Inc.||Physiological parameter analysis for an implantable restriction device and a data logger|
|US8187162||6 Mar 2008||29 May 2012||Ethicon Endo-Surgery, Inc.||Reorientation port|
|US8187163||10 Dec 2007||29 May 2012||Ethicon Endo-Surgery, Inc.||Methods for implanting a gastric restriction device|
|US8192350||28 Jan 2008||5 Jun 2012||Ethicon Endo-Surgery, Inc.||Methods and devices for measuring impedance in a gastric restriction system|
|US8221439||7 Feb 2008||17 Jul 2012||Ethicon Endo-Surgery, Inc.||Powering implantable restriction systems using kinetic motion|
|US8233995||6 Mar 2008||31 Jul 2012||Ethicon Endo-Surgery, Inc.||System and method of aligning an implantable antenna|
|US8249686||12 Sep 2008||21 Aug 2012||Corventis, Inc.||Adherent device for sleep disordered breathing|
|US8285356||10 Jan 2012||9 Oct 2012||Corventis, Inc.||Adherent device with multiple physiological sensors|
|US8337389||28 Jan 2008||25 Dec 2012||Ethicon Endo-Surgery, Inc.||Methods and devices for diagnosing performance of a gastric restriction system|
|US8374688||12 Sep 2008||12 Feb 2013||Corventis, Inc.||System and methods for wireless body fluid monitoring|
|US8377079||27 Dec 2007||19 Feb 2013||Ethicon Endo-Surgery, Inc.||Constant force mechanisms for regulating restriction devices|
|US8412317||20 Apr 2009||2 Apr 2013||Corventis, Inc.||Method and apparatus to measure bioelectric impedance of patient tissue|
|US8428682 *||16 Jun 2006||23 Apr 2013||Orbital Research Inc.||Wet or dry electrode, other sensors, actuators, or markers with a novel adhesive collar|
|US8460189||12 Sep 2008||11 Jun 2013||Corventis, Inc.||Adherent cardiac monitor with advanced sensing capabilities|
|US8469741||29 Apr 2009||25 Jun 2013||3M Innovative Properties Company||Stretchable conductive connector|
|US8591395||28 Jan 2008||26 Nov 2013||Ethicon Endo-Surgery, Inc.||Gastric restriction device data handling devices and methods|
|US8591430||12 Sep 2008||26 Nov 2013||Corventis, Inc.||Adherent device for respiratory monitoring|
|US8591532||12 Feb 2008||26 Nov 2013||Ethicon Endo-Sugery, Inc.||Automatically adjusting band system|
|US8684925||12 Sep 2008||1 Apr 2014||Corventis, Inc.||Injectable device for physiological monitoring|
|US8700118||29 Apr 2009||15 Apr 2014||3M Innovative Properties Company||Biomedical sensor system|
|US8718752||11 Mar 2009||6 May 2014||Corventis, Inc.||Heart failure decompensation prediction based on cardiac rhythm|
|US8771256||27 Oct 2010||8 Jul 2014||Eyegate Pharma S.A.||Device delivering medicines by transpalpebral electrophoresis|
|US8790257||12 Sep 2008||29 Jul 2014||Corventis, Inc.||Multi-sensor patient monitor to detect impending cardiac decompensation|
|US8790259||22 Oct 2010||29 Jul 2014||Corventis, Inc.||Method and apparatus for remote detection and monitoring of functional chronotropic incompetence|
|US8814574 *||15 Mar 2013||26 Aug 2014||Suunto Oy||Male end of a telemetric transceiver|
|US8870742||28 Feb 2008||28 Oct 2014||Ethicon Endo-Surgery, Inc.||GUI for an implantable restriction device and a data logger|
|US8897868||12 Sep 2008||25 Nov 2014||Medtronic, Inc.||Medical device automatic start-up upon contact to patient tissue|
|US8965498||28 Mar 2011||24 Feb 2015||Corventis, Inc.||Method and apparatus for personalized physiologic parameters|
|US9089273||8 Jul 2011||28 Jul 2015||Cecotepe Asbl||Textile electrode|
|US9173615||23 Sep 2014||3 Nov 2015||Medtronic Monitoring, Inc.||Method and apparatus for personalized physiologic parameters|
|US9186089||12 Sep 2008||17 Nov 2015||Medtronic Monitoring, Inc.||Injectable physiological monitoring system|
|US9192512||23 May 2014||24 Nov 2015||Eyegate Pharma S.A.S.||Device for delivering medicines by transpalpebral electrophoresis|
|US9357929||27 Jul 2010||7 Jun 2016||Carefusion 303, Inc.||System and method for monitoring body temperature of a person|
|US9411936||12 Sep 2008||9 Aug 2016||Medtronic Monitoring, Inc.||Dynamic pairing of patients to data collection gateways|
|US9420952||27 Jul 2010||23 Aug 2016||Carefusion 303, Inc.||Temperature probe suitable for axillary reading|
|US9451897||2 Dec 2010||27 Sep 2016||Medtronic Monitoring, Inc.||Body adherent patch with electronics for physiologic monitoring|
|US9538960||23 Oct 2015||10 Jan 2017||Medtronic Monitoring, Inc.||Injectable physiological monitoring system|
|US9579020||24 May 2013||28 Feb 2017||Medtronic Monitoring, Inc.||Adherent cardiac monitor with advanced sensing capabilities|
|US9615757||20 Jun 2014||11 Apr 2017||Medtronic Monitoring, Inc.||Method and apparatus for remote detection and monitoring of functional chronotropic incompetence|
|US9668667||14 Nov 2014||6 Jun 2017||Medtronic Monitoring, Inc.||Method and apparatus to measure bioelectric impedance of patient tissue|
|US9770182||2 Jul 2014||26 Sep 2017||Medtronic Monitoring, Inc.||Adherent device with multiple physiological sensors|
|US20030009097 *||17 Jun 2002||9 Jan 2003||Sheraton David A.||Electrode sensor package and application to the skin of a newborn or infant|
|US20040267188 *||11 Oct 2002||30 Dec 2004||Francine Behar||Device for delivering medicines by transpalpebral electrophoresis|
|US20060122298 *||3 Dec 2004||8 Jun 2006||3M Innovative Properties Company||Process for making pressure sensitive adhesive hydrogels|
|US20080207779 *||23 Feb 2007||28 Aug 2008||Ali Yahiaoui||Electrically conductive hydrogels|
|US20090292194 *||19 May 2009||26 Nov 2009||Corventis, Inc.||Chiropractic Care Management Systems and Methods|
|US20110065319 *||29 Apr 2009||17 Mar 2011||Oster Craig D||Stretchable conductive connector|
|US20110077497 *||29 Apr 2009||31 Mar 2011||Oster Craig D||Biomedical sensor system|
|US20110098632 *||27 Oct 2010||28 Apr 2011||Eyegate Pharma S.A.S||Device delivering medicines by transpalpebral electrophoresis|
|US20140187063 *||15 Mar 2013||3 Jul 2014||Suunto Oy||Male end of a telemetric transceiver|
|EP0013613A1 *||7 Jan 1980||23 Jul 1980||Johnson & Johnson Products Inc.||Electrosurgical grounding pad|
|EP2251366A1||11 Oct 2005||17 Nov 2010||3M Innovative Properties Company||Process for making pressure sensitive adhesive hydrogels|
|EP2407096A1||13 Jul 2010||18 Jan 2012||CECOTEPE asbl||Textile electrode|
|WO1979000042A1 *||7 Jul 1978||8 Feb 1979||A Mercuri||Biomedical electrode assembly|
|WO2009072023A1 *||18 Nov 2008||11 Jun 2009||Koninklijke Philips Electronics, N.V.||Forehead mounted impedance plethysmography system and method|
|WO2011081891A1||13 Dec 2010||7 Jul 2011||Corventis, Inc.||Body adherent patch with electronics for physiologic monitoring|
|WO2012007384A1||8 Jul 2011||19 Jan 2012||Cecotepe Asbl||Textile electrode|
|WO2016038545A1||9 Sep 2015||17 Mar 2016||Ecole Polytechnique Federale De Lausanne (Epfl)||Non-invasive drawable electrode for neuromuscular electrical stimulation and biological signal sensing|
|U.S. Classification||600/391, 600/397|
|Cooperative Classification||A61B5/0408, A61B5/411|
|European Classification||A61B5/41B, A61B5/0408|