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WO2002039086A2 - Système de détection du glucose - Google Patents

Système de détection du glucose Download PDF

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Publication number
WO2002039086A2
WO2002039086A2 PCT/US2001/051213 US0151213W WO0239086A2 WO 2002039086 A2 WO2002039086 A2 WO 2002039086A2 US 0151213 W US0151213 W US 0151213W WO 0239086 A2 WO0239086 A2 WO 0239086A2
Authority
WO
WIPO (PCT)
Prior art keywords
sensor
analyte
fluid line
glucose
person
Prior art date
Application number
PCT/US2001/051213
Other languages
English (en)
Other versions
WO2002039086A9 (fr
WO2002039086A3 (fr
WO2002039086A8 (fr
Inventor
Kirk Ramey
Chiun Liu Chiung
Original Assignee
Nipro Diabetes Systems
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Nipro Diabetes Systems filed Critical Nipro Diabetes Systems
Priority to EP01985206A priority Critical patent/EP1333751A2/fr
Priority to JP2002541361A priority patent/JP2004512914A/ja
Priority to AU2002234176A priority patent/AU2002234176A1/en
Publication of WO2002039086A2 publication Critical patent/WO2002039086A2/fr
Publication of WO2002039086A3 publication Critical patent/WO2002039086A3/fr
Publication of WO2002039086A8 publication Critical patent/WO2002039086A8/fr
Publication of WO2002039086A9 publication Critical patent/WO2002039086A9/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means using enzyme electrodes, e.g. with immobilised oxidase
    • A61B5/14865—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means using enzyme electrodes, e.g. with immobilised oxidase invasive, e.g. introduced into the body by a catheter or needle or using implanted sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6848—Needles
    • A61B5/6849—Needles in combination with a needle set

Definitions

  • the present invention relates to the sensor arts . It finds particular application in conjunction with printed electrochemical sensors of the type used, for example, in the subcutaneous or transcutaneous monitoring of blood glucose levels in a diabetic person, and will be described with particular reference thereto. It should be appreciated, however, that the invention is also applicable to the determination of other electrochemically detectable substances present in body fluids and non-body fluids.
  • Thin film electrochemical sensors are generally known in the art for use in a variety of specialized applications, including the detection of glucose. Thick film sensors are also known. Such thin or thick film sensors may comprise one or more thin conductors applied by photolithography mask and etch techniques between thin layers of a nonconductive material, such as a polyimide film. Silk screen printing techniques have also been used in the preparation of sensors. The conductors are shaped to define distal end sensor tips having an appropriate electrode material thereon, in combination with proximal end contact pads adapted for conductive connection with appropriate electronic monitoring equipment .
  • thin film sensors of this type have been proposed for use as a transcutaneous sensor in medical applications.
  • thin film sensors have been designed for monitoring blood glucose levels in a diabetic person, with the distal end sensor electrode s positioned subcutaneously in direct contact with the person's blood stream.
  • sensors typically employ an oxidase enzyme, particularly glucose oxidase.
  • the oxidase acts on a substrate or analyte, such as glucose, to produce hydrogen peroxide, and in the process, oxygen is consumed.
  • the concentration of glucose can be determined indirectly, such as by detecting the depletion of oxygen or the generation of reaction products, such as hydrogen peroxide or gluconic acid.
  • U.S. Patent No. 4,970,145 discloses electrodes formed from platinized carbon particles on which an enzyme, such. as glucose oxidase, is immobilized.
  • 5,160,416 discloses similar electrodes in which a mixture of the enzyme with finely divided platinum group metal or oxide particles and carbon powder in a suitable binder is deposited on an electrically conductive support material, such as carbon paper or a platinum strip. Both patents disclose the use of amperometric techniques to determine glucose levels.
  • the present invention provides a new and improved sensor and method of use which overcomes the above- referenced problems and others . Summary of the Invention
  • a sensor system formed by printing electrodes on a support has a variety of applications for the detection of glucose and other chemicals in vivo and in vitro.
  • One advantage of the present invention is that a disposable sensor is readily formed.
  • the senor may be formed on a wall of a catheter.
  • the invention may take form in various components and arrangements of components, and in various steps and arrangements of steps .
  • the drawings are only for purposes of illustrating a preferred embodiment and are not to be construed as limiting the invention.
  • FIGURE 1 is a top view of a sensor according to the present invention.
  • FIGURE 2 is a perspective sectional view in partial section through A-A of the sensor of FIGURE 1;
  • FIGURE 3 is a schematic view of a combination infusion pump and glucose meter according to the present invention.
  • FIGURE 4 is a schematic sectional view of a sensor inserted through the wall of a catheter
  • FIGURE 5 shows a sensor in use in a closed loop system
  • FIGURE 6 is a schematic sectional view of a subcutaneous sensor system mounted to an exterior of a catheter wall and signaling a glucose meter, according to the present invention
  • FIGURE 7 is a schematic sectional view of a subcutaneous sensor mounted to an interior of a catheter wall and signaling a glucose meter coupled to an insulin pump;
  • FIGURE 8 is a top view of a sheet of support material with sensors printed thereon;
  • FIGURE 9 is a side perspective view of the support sheet of FIGURE 8 rolled into a catheter shape with the sensors on the exterior; and
  • FIGURE 10 is a side sectional view of an infusion set with a catheter passing through a person's skin.
  • a sensor 10 is shown. While the sensor is described with reference to glucose detection, it will be appreciated that the sensor may also be used for detection of other electrochemically detectable chemicals . ;
  • the sensor comprises a support 12, formed from an insulative material, such as a sheet of polyester, polycarbonate, or polyimide.
  • the support defines a well 14 adjacent one end of its upper surface 16.
  • a sensing material 18 is deposited at the base and on the sides of the well.
  • the sensing material 18 includes an oxidoreductase enzyme, such as glucose oxidase, with is capable of catalyzing the reaction of a substrate or analyte (e.g., glucose) .
  • glucose analyte
  • the glucose oxidase enzyme acts on the glucose to produce hydrogen peroxide, the reaction consuming oxygen.
  • Suitable oxidoreductases include uricase, lactase oxidase, cholesterol oxidase, and other peroxide-producing enzymes. Combinations of enzymes may also be used, as well as combinations of non-oxidases and oxidases, the non-oxidase acting on a substrate of interest to produce an oxidizable substrate for the oxidase .
  • One such combination is beta-galactosidase and glucose oxidase for the determination of lactose.
  • the sensing material 18 preferably also includes a platinum group metal or metal oxide in finely divided form, which is relatively homogeneously mixed with the oxidase.
  • Suitable platinum group metals and oxides thereof include platinum, ruthenium, rhodium, iridium, palladium., and their oxides, and combinations thereof. Ruthenium is a particularly preferred metal.
  • the sensing material may further include a carbon-containing material, such as finely divided carbon or graphite powder. Such materials preferably have a relatively large surface area of about 10 m 3 /gm or higher, most preferably, in the range of 200-600 m 3 /g.
  • the platinum group metal or metal oxide has a particle size in the range of from about 1 nm to about 20 ⁇ , most preferably, in the range of 1-4 ⁇ m.
  • a droplet or layer of an analyte-containing liquid or viscous fluid 20 to be analyzed for the substrate is added to the well .
  • An electrode system 22 detects a product generated (e.g., hydrogen peroxide or gluconic acid) or a chemical consumed (e.g., oxygen) .
  • Hydrogen peroxide is a particularly preferred detectable substance.
  • FIGURES 1 and 2 show a 3-electrode system, with a working electrode 24, reference electrode 26, and a counter electrode 28, laid down generally in parallel on the support surface so that at least a portion of each of the electrodes is in contact with the fluid 20.
  • other electrode systems may also be employed, such as a two electrode system employing working and reference electrodes.
  • the electrode system is in electrical contact with the analyte 20.
  • the electrodes take the form of strips, laid down on the support, with contact pads 30 at a proximal end of the support for electrically connecting the electrodes with electrochemical equipment (not shown) .
  • electrochemical measurement techniques may be employed with the electrode system, including amperometric and potentiometric techniques. For example, a voltage is periodically applied between the working and reference electrodes 24, 26 and the current generated due to reduction of hydrogen peroxide measured between the working and counter electrodes . The electrode system generates an electrical signal
  • the concentration of the analyte substance to be detected e.g., glucose
  • the electrochemical monitoring system compares the detected signal with calibrated concentration/signal data and produces an output indicative of the concentration of glucose or other substance present .
  • Various conductive materials may be used for forming the electrodes.
  • the working electrode is formed from nickel or silver
  • the counter electrode is carbon
  • the reference electrode is an Ag/AgCl electrode.
  • Other materials or combinations of materials may also be used as is known in the art.
  • the electrodes may be formed by a variety of techniques, including lithography, printing, and the like.
  • the electrode materials e.g., ruthenium and glucose oxidase for the sensing material 18, are mixed together and combined with a carrier liquid to form a suspension which is deposited on the support.
  • the electrodes 24, 26, 28, and also the sensing material 18 and contact pads 30 are printed on the support material, for example by inkjet, offset, laser, silk-screen, or gravure printing techniques. Both thin and thick film printing techniques may be used.
  • Inks are prepared by combining the materials for the electrodes or sensing material with a suitable carrier, such as a liquid or a material which flows at the temperature of printing. The inks are then printed on the support and dried or otherwise fixed. The inks can be laid down in a multi-step process, by printing a first material, which is allowed to dry, followed by a second material, and so forth, until all the materials are laid down.
  • the enzyme, metal or metal oxide, and carbon powder may be mixed together with a carrier liquid to form an ink which is printed on the support. Or, the enzyme, metal or metal oxide, and carbon powder may be separately laid down, each one in a separate ink formulation.
  • a thick film process can be used to produce the sensor.
  • a silk screen printing process is preferably used.
  • the design of the sensor elements is first transferred onto a screen (which can be a metal mesh or polymer screen) by a photographic method.
  • the selected metal or conductive electrode materials can be prepared or purchased commercially in ink or paste form.
  • the ink can then be dried by heat or UN curing.
  • the carrier liquid may be an aqueous or organic liquid or combination thereof and is preferably one which is readily removed from the electrode material or sensing material after printing, e.g., by evaporation, although leave-in carriers are also contemplated.
  • the enzyme is generally sensitive to heat. The ink is therefore dried or otherwise fixed at a temperature which does not adversely affect the activity of the enzyme.
  • the sensor 10 is used outside the body to determine the glucose level in a droplet of blood or other body fluid.
  • the droplet is withdrawn from the body and placed in the well.
  • a layer 34 of a wicking material is attached to the support surface 16 over the general area of the well .
  • the droplet is applied to the wicking material and carried thereby into the well.
  • an electrochemical monitoring system such as a glucose meter 40 (See FIGURE 3) .
  • the glucose meter both supplies the applied voltage (or current) and detects the current (or voltage) signal generated. It will be appreciated that the two functions of applying voltage/current and detecting the signal generated may be performed by separate components, although for convenience these are shown as a single unit, the glucose meter.
  • FIGURE 3 shows the glucose meter in a housing 42, which also holds an infusion pump 44, although separate glucose meters are also contemplated. After applying the droplet, the sensor 10 is inserted into a suitably shaped slot 46 in the housing, the slot having electrical connectors (not shown) which electrically connect the contact pads 30 with the glucose meter.
  • the glucose meter determines the glucose concentration and signals a controller 50 (which may be integral with or separate from the glucose meter) .
  • the controller 50 calculates an appropriate response to the detected level by accessing look-up tables.
  • the controller may recommend that a dose of a medicament (e.g., a number of ml of insulin) be supplied to the person (e.g., from the infusion pump) .
  • the controller may recommend that the person ingest carbohydrate.
  • the recommended dose or other action step to be taken is displayed in human readable form, such as on a display screen 54.
  • the person may accept the recommended dose, for example by pressing keys on a keypad 56, or may enter a different dose to be taken.
  • the controller then instructs the infusion pump 44 to deliver to the selected dose, for example, by operating a motor 58 to drive a piston 60 of a syringe 66 containing the medicament .
  • the medicament e.g., insulin
  • the controller may override the person in selecting a suitable dose, so that the person is not injected with a dangerous level of the medicament.
  • the personal input 56 is eliminated and the controller instructs the insulin pump directly.
  • the senor 10 is used to detect glucose or other body chemical a body fluid flowing through tubing, such as a catheter 70 (see FIGURE 4) .
  • the support 12 is formed from a material (e.g., polyimide or polyurethane) and/or is shaped (e.g., with a rounded end 72 or pointed tip) so that it is capable of piercing the catheter wall 74.
  • the sensor support 12 is preferably formed from a rigid material and of a sufficient thickness that does not readily break during piercing. Catheters, in general, are formed from a relatively soft material, which is capable of being pierced.
  • the electrode system 22 is thereby positioned to be immersed in the body fluid or other liquid to be analyzed in the bore 76 of the catheter.
  • the well 14 and wicking membrane 34 may be eliminated as the electrodes 24,26,28 and sensor material 18 are in direct contact with the analyte.
  • the wicking membrane may be replaced with a protein-impermeable membrane or coating 80 or other membrane which inhibits the passage of materials which may be detrimental to the operation of the sensor.
  • the membrane covers those portions of the sensor which are affected by the detrimental materials, such as the electrodes and/or the sensing material.
  • the membrane 80 is, however, permeable to at least glucose (or other chemical to be detected) .
  • Suitable protein impermeable membranes may be formed from a mixture of 2-hydroxyethyl methacrylate (HE A) , N,N-dimethyl amino ethyl methacrylate (DMAEMA) and ethacrylic acid (MA) , although other protein-impermeable materials are also contemplated.
  • HE A 2-hydroxyethyl methacrylate
  • DMAEMA N,N-dimethyl amino ethyl methacrylate
  • MA ethacrylic acid
  • a coating which resists blood coagulation and protein binding may also be used, such as a mixture of polyethylene glycol (PEG) and heparin.
  • the sensor of FIGURE 4 may be employed in a loop system, such as a dialysis system (see FIGURE 5) .
  • the loop system has one fluid path defined by a first catheter 84 which carries body fluid, such as blood, from a patient's body 86 to a dialysis machine 88 or other suitable monitoring or treatment equipment.
  • a second, return catheter 90 returns the treated body fluid back to the patient.
  • the sensor 10 is inserted into one of the catheters 84, 90 (FIGURE 5 shows the sensor in the input line 84) , to detect the glucose content of the fluid flowing therethrough.
  • the sensor may be operated continuously or intermittently, every few minutes, or as appropriate, to monitor the changing glucose level.
  • the sensor is electrically connected by wiring 92 (or radio telemetry) to a glucose meter 94, which may be housed with the dialysis machine.
  • the glucose meter uses electrochemical techniques to monitor glucose levels, for example, by directing the hydrogen peroxide generated by enzymatic conversion of the glucose in a small region of the body fluid adjacent the sensing element 18.
  • the glucose meter instructs the dialysis machine 88 to cease purifying the blood or to take other appropriate action.
  • this operation may be conducted by a trained operator, who reads the glucose level detected by the glucose meter and programs the dialysis machine accordingly.
  • the senor is employed for subcutaneous monitoring of glucose concentrations.
  • the sensor 10 is mounted to a wall 100 of a catheter tube 102 such as a cannula, which may be employed to deliver insulin, or other medicament, to the persons blood or subcutaneous fluid.
  • An infusion set 104 connected with a suitable insulin pump similar to that illustrated in FIGURE 3, or other delivery apparatus, delivers insulin to the catheter, which carries the insulin through the skin 106 and into a blood vessel, e.g., an artery, or into the interstitial fluid.
  • the sensor may be positioned on an exterior surface 108 of the canula wall 100, as shown in FIGURE 6, or on an interior surface 110 of the wall, as shown in FIGURE 7.
  • the sensor 10 generates an electrical signal in response to an applied voltage or current which is related to the glucose level in the blood vessel or interstitial fluid adjacent the sensor.
  • Electrical wiring 112 (or radio telemetry) connects the sensor 10 with a glucose meter 114.
  • the glucose meter may be a separate unit (FIGURE 6) or housed together with an insulin pump 44 and controller 50 (see FIGURE 7) , analogous to that shown in FIGURE 3.
  • the senor 10 When formed on the inside of the wall (FIGURE 7) , the sensor 10 is used between dosages of insulin, when the catheter is filled primarily with interstitial fluid or blood and the • fluid line 68 to the insulin pump 44 is preferably closed off .
  • the wiring 112 may be attached to the exterior 108 of the catheter wall 100 (FIGURE 6) , attached to the interior surface 110, or integrally formed with the catheter wall 100 so that it is encased by the catheter wall (FIGURE 7) .
  • the electrodes 24, 26, 28 and sensing material 18 of the sensor 10, and optionally also a portion of the wiring 112 are applied directly to a surface 108, 110 of the catheter wall 100.
  • the catheter wall 100 thus provides the support 12 for the sensor.
  • the sensor may be formed, as shown in FIGURES 6 and 7, on an exterior or interior wall of the catheter, either by printing a preformed catheter or by forming the sensor components on a sheet 120 which is then rolled into the shape of the catheter and joined at a seam 122, either by welding or with a suitable adhesive.
  • the application of the sensor components 18, 24, 26, 28,30 is preferably achieved by printing the components on the sheet 120 or formed catheter, although other application methods are also contemplated. As shown in FIGURES 8 and 9, a number (two are shown) of sensors 10, 10' may be printed on a single catheter. As for the embodiment of FIGURE 4, a protein impermeable membrane 80 is preferably formed over the sensor.
  • the wiring 112 may be carried by the catheter 102 to a cannula housing 130 of the infusion set 104.
  • the infusion set comprises the cannula housing, which holds the upstream end of the catheter 102, and an injection hub 132, which carries a needle 136.
  • the injection hub is selectively linked to the cannula housing to supply insulin to the catheter via the needle 136.
  • the needle is fluidly connected with the fluid line 68 and carries the medicament through a septum 138, mounted at the upstream end of the catheter, into the catheter bore.
  • the wiring 112 is connected to the glucose meter via a connection made when the hub 132 and cannula housing 130 are linked. Additional wiring 140 may be attached to the fluid line 68, in a similar manner to wiring 112, to electrically connect the wiring 112 with the glucose meter 114, or radio telemetry may be used to transfer the signal thereto.
  • the cannula 102 with the sensor 10 formed thereon is inserted into the person's body with an insertion needle (not shown) , for example, by replacing the injection hub 132 of the infusion set 104 with an insertion hub having a needle which extends through the cannula to just beyond the distal end of the cannula.
  • the needle is inserted through the skin, carrying the cannula with it.
  • the sensor is then ready for use.
  • the sensor may be used continuously or intermittently to provide glucose measurements over a period of hours or several days .
  • diabetics change the site of insulin injection every few days to prevent damage to the skin.
  • a fresh catheter is inserted into the skin, accompanied by a fresh sensor 10 or sensors.
  • the sensor is preferably configured (for example, with a protein- impermeable membrane) so that the signal does not degrade appreciably within the period of use, preferably functioning effectively for several days, or more.
  • the catheter with the sensor 10 printed thereon need not be used with an infusion set 104 as shown in FIGURES 6 and 7, but may be used with other methods of drug delivery, or may be used with a blood treatment system, such as the dialysis unit of FIGURE 5.
  • the sensor 10 may also include a heating element 150, such as a resistance heater, which is .formed on the support 12 in a similar manner to the other components (such as by printing) .
  • the element may be formed from platinum or other suitable metal. Electrical current is supplied to the heating element 150 via leads 152, 154, which are also printed on the support 12.
  • the heater is used to maintain the analyte at an appropriate temperature for measuring glucose concentration (i.e., by changes in H 2 0 2 or 0 2 concentration) . Since the rate of the enzyme catalyzed reaction between glucose and oxygen is dependent on the temperature of the analyte fluid, it is preferable for the sensor to operate at a predetermined selected temperature .
  • the heater can also be used as a temperature detector, detecting the temperature of the adjacent fluid by measuring the voltage across the resistance heater at a determined applied current.
  • the heater may be formed on an opposite surface of the support to that carrying the electrodes 24,26,28 and sensing element 18 (except where the catheter is used as the sensor support) .
  • the sensor may also be configured to measure other properties of the analyte solution, such as pH.
  • FIGURE 1 shows a pH detector 160 formed on the surface 16 of the support 12 (e.g., by printing). Additionally or alternatively, the sensor may be adapted to measure ketones, which can build up to dangerous levels, particularly in the blood of diabetics. While the sensor is particularly applicable to detecting glucose in blood and other body fluids of humans, it may also be used in other animals and for detection of glucose and other analytes in non-body fluids .

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Abstract

La présente invention concerne une sonde (10) de détection d'un analysat tel que le glucose dans un fluide tel que le sang ou un autre fluide anatomique. A cet effet, on imprime sur un support approprié (12) d'une part les composants de la sonde tels que des électrodes (24, 36, 38) et d'autre part un élément de détection (18) contenant une oxydoréductase telle que l'oxydase du glucose. Selon un mode de réalisation, le support comprend la paroi (100) d'un cathéter (102) inséré dans l'anatomie d'un patient.
PCT/US2001/051213 2000-11-13 2001-11-13 Système de détection du glucose WO2002039086A2 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP01985206A EP1333751A2 (fr) 2000-11-13 2001-11-13 Syst me de d tection du glucose
JP2002541361A JP2004512914A (ja) 2000-11-13 2001-11-13 グルコースセンサーシステム
AU2002234176A AU2002234176A1 (en) 2000-11-13 2001-11-13 Glucose sensor system

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US24811800P 2000-11-13 2000-11-13
US60/248,118 2000-11-13

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WO2002039086A2 true WO2002039086A2 (fr) 2002-05-16
WO2002039086A3 WO2002039086A3 (fr) 2003-04-03
WO2002039086A8 WO2002039086A8 (fr) 2003-05-30
WO2002039086A9 WO2002039086A9 (fr) 2003-06-26

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WO2006102412A2 (fr) 2005-03-21 2006-09-28 Abbott Diabetes Care, Inc. Procede et systeme permettant d'obtenir un systeme de controle de substance a analyser et de perfusion de medicament integre
JP2006523846A (ja) * 2003-04-15 2006-10-19 オプテイスカン・バイオメデイカル・コーポレーシヨン 双測定被検体検出システム
WO2009060432A1 (fr) * 2007-11-07 2009-05-14 Medingo Ltd. Dispositif et procédé de prévention contre des complications diabétiques
WO2009090392A1 (fr) * 2008-01-18 2009-07-23 Lifescan Scotland Limited Procédé et système de fabrication de lots de bandelettes réactives présentant une caractéristique d'étalonnage prédéterminée
WO2010106781A1 (fr) * 2009-03-16 2010-09-23 Arkray, Inc. Procédé de mesure continue d'une concentration de substrat
EP2260759A3 (fr) * 2005-06-17 2010-12-29 F. Hoffmann-La Roche AG Système de capteur, disposition et méthode pour surveiller un composé, en particulier le glucose dans le tissu du corps.
CN103285448A (zh) * 2005-05-17 2013-09-11 爱森斯有限公司 药物递送和分析物传感器相结合的装置
WO2014037745A1 (fr) * 2012-09-07 2014-03-13 Lifescan Scotland Limited Bandelette d'essai analytique à base électrochimique avec des électrodes interférentes nues
US20140213869A1 (en) * 2006-10-04 2014-07-31 Dexcom, Inc. Analyte sensor
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US9636450B2 (en) 2007-02-19 2017-05-02 Udo Hoss Pump system modular components for delivering medication and analyte sensing at seperate insertion sites
US9697332B2 (en) 2006-08-07 2017-07-04 Abbott Diabetes Care Inc. Method and system for providing data management in integrated analyte monitoring and infusion system
US9750440B2 (en) 2005-05-17 2017-09-05 Abbott Diabetes Care Inc. Method and system for providing data management in data monitoring system
US9795326B2 (en) 2009-07-23 2017-10-24 Abbott Diabetes Care Inc. Continuous analyte measurement systems and systems and methods for implanting them
US10052055B2 (en) 2003-08-01 2018-08-21 Dexcom, Inc. Analyte sensor
US10117614B2 (en) 2006-02-28 2018-11-06 Abbott Diabetes Care Inc. Method and system for providing continuous calibration of implantable analyte sensors
US10220145B2 (en) 2006-06-30 2019-03-05 Abbott Diabetes Care Inc. Integrated analyte sensor and infusion device and methods therefor
US10780222B2 (en) 2015-06-03 2020-09-22 Pacific Diabetes Technologies Inc Measurement of glucose in an insulin delivery catheter by minimizing the adverse effects of insulin preservatives
US10872102B2 (en) 2009-07-23 2020-12-22 Abbott Diabetes Care Inc. Real time management of data relating to physiological control of glucose levels
US10980461B2 (en) 2008-11-07 2021-04-20 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US11000215B1 (en) 2003-12-05 2021-05-11 Dexcom, Inc. Analyte sensor
US11229382B2 (en) 2013-12-31 2022-01-25 Abbott Diabetes Care Inc. Self-powered analyte sensor and devices using the same
US11517652B2 (en) 2017-03-24 2022-12-06 Fresenius Medical Care Deutschland Gmbh Medical device with an additively applied converter
US11712504B2 (en) 2017-03-24 2023-08-01 Fresenius Medical Care Deutschland Gmbh Medical device with additively applied converter including a conductive path

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EP1333751A2 (fr) 2003-08-13
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JP2004512914A (ja) 2004-04-30
WO2002039086A8 (fr) 2003-05-30

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