JP2001057967A - Production of biotic electrode - Google Patents
Production of biotic electrodeInfo
- Publication number
- JP2001057967A JP2001057967A JP2000190595A JP2000190595A JP2001057967A JP 2001057967 A JP2001057967 A JP 2001057967A JP 2000190595 A JP2000190595 A JP 2000190595A JP 2000190595 A JP2000190595 A JP 2000190595A JP 2001057967 A JP2001057967 A JP 2001057967A
- Authority
- JP
- Japan
- Prior art keywords
- film
- conductive
- vinyl chloride
- vinyl
- ethylene
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
Landscapes
- Electrotherapy Devices (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】本発明は生体用電極の製造方法に
関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a method for manufacturing a biological electrode.
【０００２】[0002]
【従来例】生体用電極は、主に導電性粘着ゲルと導電性
部材と電気的絶縁性を供えた支持部材の積層構造よりな
る。導電性粘着ゲルは、自己粘着性によって生体、導電
性部材並びに支持部材と接合し、又、導電性部材と支持
部材とは、接着剤、粘着剤、機械的結合、印刷手段を利
用して接合している。ところで、生体用電極は、生体表
面のインターフェースを司る故に、全体として薄さ、柔
軟さを基調とするところ、支持部材と導電性部材との接
合態様として、カーボン、銀等の導電粉末乃至ペースト
を印刷、焼付けして導電性部材を支持部材上に配置した
ものが、薄さ、柔軟さ及び両者の結合の強さ等に於いて
他のものより秀れている。2. Description of the Related Art A biological electrode mainly has a laminated structure of a conductive adhesive gel, a conductive member and a support member having electrical insulation. The conductive adhesive gel is bonded to a living body, a conductive member, and a support member by self-adhesion, and the conductive member and the support member are bonded using an adhesive, a pressure-sensitive adhesive, a mechanical bond, and a printing means. are doing. By the way, since the biological electrode controls the interface of the surface of the living body, it is based on thinness and flexibility as a whole.As a bonding mode between the support member and the conductive member, a conductive powder or paste such as carbon or silver is used. The printed and baked conductive member disposed on the support member is superior to the others in terms of thinness, flexibility and strength of the connection between them.
【０００３】[0003]
【発明が解決しようとする課題】しかしながら、加熱し
た際、材料に耐熱性があっても、支持部材の厚みを小さ
くすると変形やしわが生じやすくなったり、支持部材の
伸縮性が増加する為、装着した導電性部材が剥れやすく
なること等の欠点を有していた。However, even when the material has heat resistance when heated, if the thickness of the supporting member is reduced, deformation or wrinkling is liable to occur, and the elasticity of the supporting member is increased. There is a drawback that the mounted conductive member is easily peeled off.
【０００４】[0004]
【課題を解決するための手段】上記に鑑み本発明は、数
枚のシートを積層した複合支持部材、前記複合支持部材
表面に導電性インクを印刷焼付け処理を施してなる導電
性部材及び導電性粘着ゲルの積層構造とすることによ
り、上記課題を解決した生体用電極を実現した。SUMMARY OF THE INVENTION In view of the above, the present invention provides a composite support member in which several sheets are laminated, a conductive member formed by printing and baking a conductive ink on the surface of the composite support member, and a conductive member. By adopting a laminated structure of the adhesive gel, a living body electrode that solves the above problem has been realized.
【０００５】本発明で示す生体用電極とは、心電計、脈
波計等生体から信号を検出する為の生体用電極、及び、
低周波治療器等生体に電気刺激を加える為の導子等を示
すものである。[0005] The living body electrode described in the present invention includes a living body electrode for detecting a signal from a living body such as an electrocardiograph and a pulse wave meter, and
It shows a conductor and the like for applying electrical stimulation to a living body such as a low frequency treatment device.
【０００６】複合支持部材とは、複数の薄いフィルムを
粘着剤又は接着剤で貼り合わせて形成したものである。
導電性部材を装着する側のフィルム（第１フィルム）
は、耐熱性と柔軟性を有するフィルムで形成されるが、
その材料としてポリエチレンテレフタレート、ポリサル
ホン系樹脂（ポリエーテルサルホン、ユーデル・ポリサ
ルホン）、ポリカーボネート、ポリイミド等が例示され
る。又、印刷後の焼付けの温度あるいは焼付けと同様で
あるが他の方法、例えばＵＶや電子線を用いれば、ポリ
アセテートフィルム等の使用も可能である。The composite support member is formed by laminating a plurality of thin films with an adhesive or an adhesive.
Film on the side where the conductive member is mounted (first film)
Is formed of a film having heat resistance and flexibility,
Examples of the material include polyethylene terephthalate, polysulfone resins (polyethersulfone, Udel polysulfone), polycarbonate, polyimide and the like. The temperature of printing after printing or the same as printing, but using other methods, for example, UV or electron beam, it is also possible to use a polyacetate film or the like.
【０００７】前記第１のフィルムに対し他のフィルム
（第２のフィルム）は、軟らかく、外見上、風合いの良
いものであればよく、その材料としては、塩化ビニル、
エチレン−塩ビ共重合体、エチレン−酢ビ共重合体、塩
化ビニリデン、塩素化塩化ビニル、塩素化ポリエチレ
ン、ポリビニルブチラール、ポリビニルホルマール、天
然ゴム、イソプレンゴム、ポリウレタン、ポリエチレ
ン、ブタジエンゴムのフィルム又はフォームシート等が
例示される。第１のフィルム、第２のフィルムは、各々
が単に耐熱性、風合いを供えているだけであり、従来材
料として使用されているものも含まれてはいる。しかし
ながら、本発明はこれらを貼り合わせ積層させること
で、伸縮性を抑制し、導電性部材を印刷焼付けによって
装着する際フィルムに加えられる熱によって変形、しわ
等が生ずることなく、しかも長期間使用しても、しわ、
歪みが可及的に抑制される等の相乗的な効果を発揮させ
ているのである。しかも、各々のフィルムの厚さは数百
μ以下と極薄いものである為、粘着剤、接着剤を介して
も従来のものと同じかそれよりも薄い為、より柔軟性に
秀れているものである。The other film (the second film) may be soft and have a good texture in appearance, as compared to the first film.
Ethylene-vinyl chloride copolymer, ethylene-vinyl acetate copolymer, vinylidene chloride, chlorinated vinyl chloride, chlorinated polyethylene, polyvinyl butyral, polyvinyl formal, natural rubber, isoprene rubber, polyurethane, polyethylene, butadiene rubber film or foam sheet Etc. are exemplified. The first film and the second film merely provide heat resistance and texture, respectively, and include those conventionally used as materials. However, the present invention suppresses the elasticity by laminating and laminating them, and does not cause deformation, wrinkles, etc. due to the heat applied to the film when the conductive member is attached by printing and printing, and can be used for a long time. Even wrinkles,
Synergistic effects such as suppressing distortion as much as possible are exhibited. Moreover, since the thickness of each film is extremely thin, not more than several hundred μ, it is excellent in flexibility because it is the same as or thinner than the conventional one even through an adhesive or an adhesive. Things.
【０００８】更に安価であることは、上記材料が従来、
生体用電極の支持部材として使用されているものを適用
できる点で明らかである。尚、フィルムの枚数は２枚以
上であればよく特に限定されない。[0008] The fact that the material is inexpensive means that
It is clear that the material used as the support member for the biological electrode can be applied. The number of films is not particularly limited as long as it is two or more.
【０００９】本発明で、導電性部材は、支持部材上に導
電性インクを印刷焼付けによって形成されることが好ま
しいが、次に導電性インクの成分の一例を次に示す。導
電性インクの成分は、溶剤を除きバインダーと分散粉
（導電性粉体）の２つに分かれる。バインダー種（セラ
ミック用、シリコン用含む）としては、塩ビ系、ポリエ
ステル系、フェノール系、ポリアミド系、アクリル系、
ウレタン系、ポリイミド系、エポキシ系、フロロエラス
トマー系等が例示される。分散粉（導電性粉体）として
は、カーボン、金属粉（銀、ニッケル、スズ、アルミニ
ウム、銅）、酸化金属（酸化スズ）、ハンダ（ペースト
としてＴｉ、Ａｕ、Ｐｔ、ＳＵＳ等）等が例示される。
又、これらカーボンと金属粉とを並用してもよい。尚、
好ましくは、カーボンとグラファイトの混合粉が使用さ
れる。In the present invention, the conductive member is preferably formed by printing and printing a conductive ink on the support member. Next, examples of the components of the conductive ink are shown below. The components of the conductive ink are divided into a binder and a dispersed powder (conductive powder) except for the solvent. Binder types (including ceramic and silicon) include PVC, polyester, phenol, polyamide, acrylic,
Examples thereof include urethane-based, polyimide-based, epoxy-based, and fluoroelastomer-based materials. Examples of the dispersed powder (conductive powder) include carbon, metal powder (silver, nickel, tin, aluminum, copper), metal oxide (tin oxide), solder (Ti, Au, Pt, SUS, etc. as paste). Is done.
Further, these carbon and metal powder may be used together. still,
Preferably, a mixed powder of carbon and graphite is used.
【００１０】導電性部材は、上記材料を使用して印刷焼
付け処理によって形成される他、銀パターンによって導
電性部材を形成した後、更にその上からカーボンパター
ンによって導電性部材を形成したいわゆる多重積層状の
ものであってもよい。尚、バインダーに於いては、低周
波治療器等の導子を形成する場合、低周波治療器の低周
波出力パルスの直流分によってバインダー自身に加水分
解が生じる為、使用不能となる組材が多いがこれらの中
で、使用に耐え得るものとして塩ビ系が好適に選択され
る。本発明で示す導電性粘着ゲルは、従来使用されてい
るものであればいかなるものであってもよく、特に限定
されない。又、厚みを少なくする為に更に、不繊布、チ
ュール等を介在させてもよい。The conductive member is formed by printing and baking using the above-mentioned materials. In addition, the conductive member is formed by a silver pattern, and then the conductive member is formed by a carbon pattern thereon. Shape. In the case of forming a conductor for a low-frequency therapeutic device or the like in the binder, since the binder itself is hydrolyzed by the direct current component of the low-frequency output pulse of the low-frequency therapeutic device, the unusable assembly material is used. Of these, among these, a PVC system is suitably selected as one that can be used. The conductive adhesive gel shown in the present invention may be any one as long as it is conventionally used, and is not particularly limited. Further, in order to reduce the thickness, a non-woven cloth, tulle or the like may be further interposed.
【００１１】[0011]
【実施例】図１及び図２は本発明の一実施例を示す図で
あり、図１は、図２で示す底面図をＡ−Ａ′で切断した
際の断面を示す。(１)は、第１フィルムであり、上述し
た組材よりなる柔軟且つ薄型で耐熱性を有するフィルム
である。(２)は、第２フィルムであり、上述した組材よ
りなる柔軟且つ薄型のフィルムである。第１フィルム
(１)と第２フィルム(２)とは、粘着剤乃至接着剤で接合
している。接合層を(７)に示す。(３)は、導電性部材で
あり、上述した組材を第１フィルム(１)の片面に印刷、
焼付け処理を施して形成したものである。又、導電性部
材(３)は、図２で示す様に網目状のパターンで印刷され
ている。(５)は、導電性粘着シートであり、上述した組
材よりなる。導電性粘着シート(５)は、導電性部材(３)
と接合している。この接合は、導電性粘着シート(５)の
粘着力によって行なわれる。(６)は、端子部であり、第
１フィルム(１)、第２フィルム(２)、導電性部材(３)が
延長されることによって形成されている。(４)は、孔部
であり、端子部(６)と外部装置から延びた接続具（図示
せず）とが、固く接合される為に設けられている。1 and 2 show an embodiment of the present invention. FIG. 1 is a sectional view taken along the line AA 'of the bottom view shown in FIG. (1) is a first film, which is a flexible, thin, and heat-resistant film made of the above-described assembled material. (2) is a second film, which is a flexible and thin film made of the above-mentioned assembled material. 1st film
(1) and the second film (2) are joined with an adhesive or an adhesive. The bonding layer is shown in (7). (3) is a conductive member, and the above-described assembly is printed on one side of the first film (1);
It is formed by baking. The conductive member (3) is printed in a mesh pattern as shown in FIG. (5) is a conductive adhesive sheet, which is made of the above-described assembly. The conductive adhesive sheet (5) is a conductive member (3)
And joined. This joining is performed by the adhesive force of the conductive adhesive sheet (5). (6) is a terminal portion, which is formed by extending the first film (1), the second film (2), and the conductive member (3). A hole (4) is provided so that the terminal portion (6) and a connector (not shown) extending from an external device are firmly joined.
【００１２】図３及び図４は、本発明の一実施例を示す
図であり、図３は図４で示す底面図をＢ−Ｂ′で切断し
た際の断面を示す図である。各構成は、図１及び図２と
同一であるが、更に第２フィルム(２)面に２つの導電性
部材を配したものである。片方の構成を示す数字の上に
ダッシュを付して区別した。3 and 4 are views showing an embodiment of the present invention. FIG. 3 is a view showing a cross section of the bottom view shown in FIG. 4 taken along line BB '. Each configuration is the same as in FIGS. 1 and 2, but further comprises two conductive members on the second film (2) surface. A dash is added to the numeral indicating one of the components to distinguish them.
【００１３】図３乃至図４で示す実施例を皮膚一体貼着
型低周波治療器に使用した場合の実施態様を図５に示
す。(１)〜(５)、(１′)〜(５′)は、図３乃至図４で示
した構成と同一であることから説明は省略する。(31)
は、パワーサプライユニットであり、ボタン電池等の小
型電池、及び低周波パルスを形成出力する為の電子回路
及びこれを実装した電子回路基板を内蔵する。(32)は、
導電接続具であり、パワーサプライユニット(31)の正出
力端と導電性部材(３)とを孔部(４)端子部(６)を介して
電気的、機械的に着脱自在に接続させるものである。(3
2′)も導電接続具である。導電接続具(32′)は、パワー
サプライユニット(31)の負出力端と、導電性部材(３′)
とを孔部(４′)、端子部(６′)とを介して電気的、機械
的に接続させるものである。FIG. 5 shows an embodiment in which the embodiment shown in FIGS. 3 and 4 is used for a low-frequency therapeutic device integrated with skin. (1) to (5) and (1 ') to (5') are the same as those shown in FIGS. (31)
Is a power supply unit, which incorporates a small battery such as a button battery, an electronic circuit for forming and outputting a low-frequency pulse, and an electronic circuit board on which the electronic circuit is mounted. (32) is
A conductive connecting device that electrically and mechanically detachably connects the positive output terminal of the power supply unit (31) and the conductive member (3) via the hole (4) and the terminal (6). It is. (3
2 ') is also a conductive connector. The conductive connector (32 ') is connected to the negative output terminal of the power supply unit (31) and the conductive member (3').
Are electrically and mechanically connected via the hole (4 ') and the terminal (6').
【００１４】図６は、生体（ＭＭ）の一部分に図５で示
した実施態様を貼着、使用した例を示すものである。図
５は、図６で示した斜視図のＣ−Ｃ′部を切断したその
断面を示す図である。本実施例は、生体（ＭＭ）の様々
な曲面に対し、柔軟に対応し、しかもパワーサプライユ
ニットの様な硬質ケースを装着した状態で、且つ、生体
の動き及び外部揺動を受ける中でパワーサプライユニッ
トを充分に保持し、しかも第２フィルム上にシワを生ぜ
ずに生体に貼着した状態を保つことができる点で好適な
一例である。FIG. 6 shows an example in which the embodiment shown in FIG. 5 is attached to a part of a living body (MM) and used. FIG. 5 is a view showing a cross-section taken along the line CC ′ of the perspective view shown in FIG. This embodiment flexibly copes with various curved surfaces of a living body (MM), and furthermore, in a state where a hard case such as a power supply unit is mounted, and in a state where the living body is subjected to movement and external swing. This is a preferred example in that the supply unit can be sufficiently held and can be kept attached to a living body without wrinkles on the second film.
【００１５】次に導電性粘着ゲルの一例を示す。 成 分 含有量（重量％） （イソブチレン／無水マレイン酸） ２４ 交互共重合体 ジプロピレングコール又はプロピレングリコール ３７ 濃グリセリン ９ 塩化ナトリウム １ ポリグリセリンポリグリシジルエーテル ４ 水酸化ナトリウム（ｐＨ調整剤） ５ 精製水 ２０ 製法：上記成分を混合する。Next, an example of the conductive adhesive gel will be described. Ingredient Content (% by weight) (isobutylene / maleic anhydride) 24 alternating copolymer dipropylene glycol or propylene glycol 37 concentrated glycerin 9 sodium chloride 1 polyglycerin polyglycidyl ether 4 sodium hydroxide (pH adjuster) 5 purification Water 20 Production method: The above components are mixed.
【００１６】[0016]
【発明の効果】以上詳述の如く本発明は、加熱による変
形やしわが生じにくい為、導電性部材の印刷処理装着に
適しており、しかも伸縮性が低いことから、柔軟性及び
耐久性を向上させることができ、しかも外観上の風合い
が良く安価であること等の効果を有する。As described in detail above, the present invention is less likely to be deformed or wrinkled by heating, so that it is suitable for mounting a conductive member in a printing process, and has low elasticity, so that flexibility and durability are reduced. It can be improved, and has effects such as good appearance and low cost.
【図１】本発明の一実施例を示す図である。FIG. 1 is a diagram showing one embodiment of the present invention.
【図２】本発明の一実施例を示す図である。FIG. 2 is a diagram showing one embodiment of the present invention.
【図３】本発明の他の実施例を示す図である。FIG. 3 is a diagram showing another embodiment of the present invention.
【図４】本発明の他の実施例を示す図である。FIG. 4 is a diagram showing another embodiment of the present invention.
【図５】本発明の他の実施例を示す図である。FIG. 5 is a diagram showing another embodiment of the present invention.
【図６】本発明の他の実施例を示す図である。FIG. 6 is a diagram showing another embodiment of the present invention.
１ 第１フィルム ２ 第２フィルム ３ 導電性部材 ４ 孔部 ５ 導電性粘着ゲル ６ 端子部 ７ 接着層 REFERENCE SIGNS LIST 1 first film 2 second film 3 conductive member 4 hole 5 conductive adhesive gel 6 terminal 7 adhesive layer
Claims (1)
ンテレフタレート、ポリサルホン系樹脂（ポリエーテル
サルホン、ユーデル・ポリサルホン）、ポリカーボネー
ト、ポリイミドより選ばれてなる第１のフィルムと、外
観上風合いがよく柔軟性を有するものであって、薄く成
形された塩化ビニル、エチレン−塩ビ共重合体、エチレ
ン−酢ビ共重合体、塩化ビニリデン、塩素化塩化ビニ
ル、塩素化ポリエチレン、ポリビニルブチラール、ポリ
ビニルホルマール、天然ゴム、イソプレンゴム、ポリウ
レタン、ポリエチレン、ブタジエンゴムより選ばれてな
る第２のフィルムを張り合わせた薄いシート状の複合支
持部材の第１のフイルム面に外部との電気的接続部を有
する導電パターンを導電性インクを用いて印刷し、焼き
付け処理して導電性部材を形成した後、前記導電性部材
面に導電性ゲルを貼着する生体用電極の製造方法。1. A first film made of a thin, flexible polyethylene terephthalate, polysulfone-based resin (polyethersulfone, Udel polysulfone), polycarbonate, or polyimide; And thinly molded vinyl chloride, ethylene-vinyl chloride copolymer, ethylene-vinyl acetate copolymer, vinylidene chloride, chlorinated vinyl chloride, chlorinated polyethylene, polyvinyl butyral, polyvinyl formal, natural rubber A conductive pattern having an electrical connection to the outside on a first film surface of a thin sheet-shaped composite supporting member laminated with a second film selected from isoprene rubber, polyurethane, polyethylene and butadiene rubber; Printed with ink and baked for conductivity After forming the timber, manufacturing method of the biomedical electrode of attaching a conductive gel to the conductive member surface.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2000190595A JP2001057967A (en) | 2000-01-01 | 2000-06-26 | Production of biotic electrode |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2000190595A JP2001057967A (en) | 2000-01-01 | 2000-06-26 | Production of biotic electrode |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JP2001057967A true JP2001057967A (en) | 2001-03-06 |
Family
ID=18690039
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2000190595A Pending JP2001057967A (en) | 2000-01-01 | 2000-06-26 | Production of biotic electrode |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2001057967A (en) |
Cited By (14)
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| JP2008142541A (en) * | 2006-12-08 | 2008-06-26 | General Electric Co <Ge> | Self-adhering electrode and manufacturing method thereof |
| US7761147B2 (en) | 2001-04-04 | 2010-07-20 | Alza Corporation | Transdermal electrotransport delivery device including an antimicrobial compatible reservoir composition |
| JP2014236982A (en) * | 2010-05-12 | 2014-12-18 | イリズム・テクノロジーズ・インコーポレイテッドＩｒｈｙｔｈｍ Ｔｅｃｈｎｏｌｏｇｉｅｓ，Ｉｎｃ． | Device mechanism for long adhesivity, and component |
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| WO2020003694A1 (en) * | 2018-06-29 | 2020-01-02 | 株式会社村田製作所 | Electrode to be attached to living body, and method for manufacturing electrode to be attached to living body |
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2000
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| US7761147B2 (en) | 2001-04-04 | 2010-07-20 | Alza Corporation | Transdermal electrotransport delivery device including an antimicrobial compatible reservoir composition |
| US7801599B2 (en) | 2001-04-04 | 2010-09-21 | Alza Corporation | Transdermal electrotransport delivery device including an antimicrobial compatible reservoir composition |
| JP2008142541A (en) * | 2006-12-08 | 2008-06-26 | General Electric Co <Ge> | Self-adhering electrode and manufacturing method thereof |
| US8626258B2 (en) | 2006-12-08 | 2014-01-07 | General Electric Company | Self-adhering electrodes and methods of making the same |
| JP7096869B2 (en) | 2010-05-12 | 2022-07-06 | アイリズム・テクノロジーズ・インコーポレイテッド | Electronic device |
| JP2014236982A (en) * | 2010-05-12 | 2014-12-18 | イリズム・テクノロジーズ・インコーポレイテッドＩｒｈｙｔｈｍ Ｔｅｃｈｎｏｌｏｇｉｅｓ，Ｉｎｃ． | Device mechanism for long adhesivity, and component |
| US11141091B2 (en) | 2010-05-12 | 2021-10-12 | Irhythm Technologies, Inc. | Device features and design elements for long-term adhesion |
| US10405799B2 (en) | 2010-05-12 | 2019-09-10 | Irhythm Technologies, Inc. | Device features and design elements for long-term adhesion |
| US10517500B2 (en) | 2010-05-12 | 2019-12-31 | Irhythm Technologies, Inc. | Device features and design elements for long-term adhesion |
| JP2020203140A (en) * | 2010-05-12 | 2020-12-24 | アイリズム・テクノロジーズ・インコーポレイテッドｉＲｈｙｔｈｍ Ｔｅｃｈｎｏｌｏｇｉｅｓ，Ｉｎｃ． | Device features and design elements for long-term adhesion |
| US10555683B2 (en) | 2013-01-24 | 2020-02-11 | Irhythm Technologies, Inc. | Physiological monitoring device |
| US11627902B2 (en) | 2013-01-24 | 2023-04-18 | Irhythm Technologies, Inc. | Physiological monitoring device |
| US10271754B2 (en) | 2013-01-24 | 2019-04-30 | Irhythm Technologies, Inc. | Physiological monitoring device |
| US11051738B2 (en) | 2013-01-24 | 2021-07-06 | Irhythm Technologies, Inc. | Physiological monitoring device |
| US9451975B2 (en) | 2013-04-08 | 2016-09-27 | Irhythm Technologies, Inc. | Skin abrader |
| US10098559B2 (en) | 2014-10-31 | 2018-10-16 | Irhythm Technologies, Inc. | Wearable monitor with arrhythmia burden evaluation |
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| US10299691B2 (en) | 2014-10-31 | 2019-05-28 | Irhythm Technologies, Inc. | Wearable monitor with arrhythmia burden evaluation |
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| US10939870B2 (en) | 2015-02-09 | 2021-03-09 | Murata Vios, Inc. | Patient worn sensor assembly |
| US11839756B2 (en) | 2017-12-04 | 2023-12-12 | Atlantic Therapeutics Group Limited | Conductive circuit |
| JP2021505332A (en) * | 2017-12-04 | 2021-02-18 | アトランティック セラピューティックス グループ リミテッドＡｔｌａｎｔｉｃ Ｔｈｅｒａｐｅｕｔｉｃｓ Ｇｒｏｕｐ Ｌｉｍｉｔｅｄ | Conductive circuit |
| WO2020003694A1 (en) * | 2018-06-29 | 2020-01-02 | 株式会社村田製作所 | Electrode to be attached to living body, and method for manufacturing electrode to be attached to living body |
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| US11246524B2 (en) | 2020-02-12 | 2022-02-15 | Irhythm Technologies, Inc. | Non-invasive cardiac monitor and methods of using recorded cardiac data to infer a physiological characteristic of a patient |
| US11382555B2 (en) | 2020-02-12 | 2022-07-12 | Irhythm Technologies, Inc. | Non-invasive cardiac monitor and methods of using recorded cardiac data to infer a physiological characteristic of a patient |
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| US11504041B2 (en) | 2020-08-06 | 2022-11-22 | Irhythm Technologies, Inc. | Electrical components for physiological monitoring device |
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| US11350865B2 (en) | 2020-08-06 | 2022-06-07 | Irhythm Technologies, Inc. | Wearable device with bridge portion |
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| US11337632B2 (en) | 2020-08-06 | 2022-05-24 | Irhythm Technologies, Inc. | Electrical components for physiological monitoring device |
| US11246523B1 (en) | 2020-08-06 | 2022-02-15 | Irhythm Technologies, Inc. | Wearable device with conductive traces and insulator |
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