[go: up one dir, main page]

US20060134713A1 - Biosensor apparatus and methods of use - Google Patents

Biosensor apparatus and methods of use Download PDF

Info

Publication number
US20060134713A1
US20060134713A1 US11/284,097 US28409705A US2006134713A1 US 20060134713 A1 US20060134713 A1 US 20060134713A1 US 28409705 A US28409705 A US 28409705A US 2006134713 A1 US2006134713 A1 US 2006134713A1
Authority
US
United States
Prior art keywords
reaction chamber
chamber
biosensor
sample
probe conjugate
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.)
Abandoned
Application number
US11/284,097
Other languages
English (en)
Inventor
Dennis Rylatt
Alastair Hodges
Ronald Chatelier
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Universal Biosensors Pty Ltd
Original Assignee
LifeScan Inc
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
Priority claimed from US10/105,050 external-priority patent/US20030180814A1/en
Priority claimed from US10/830,841 external-priority patent/US8685714B2/en
Priority to US11/284,097 priority Critical patent/US20060134713A1/en
Application filed by LifeScan Inc filed Critical LifeScan Inc
Assigned to LIFESCAN, INC. reassignment LIFESCAN, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: CHATELIER, RONALD, HODGES, ALASTAIR, RYLATT, DENNIS
Publication of US20060134713A1 publication Critical patent/US20060134713A1/en
Priority to JP2006312451A priority patent/JP5288700B2/ja
Priority to SI200631079T priority patent/SI1788391T1/sl
Priority to CNA2006101493105A priority patent/CN1975421A/zh
Priority to EP06255939A priority patent/EP1788391B1/en
Priority to AT06255939T priority patent/ATE509274T1/de
Priority to PL06255939T priority patent/PL1788391T3/pl
Priority to ES06255939T priority patent/ES2365169T3/es
Priority to EP10179412A priority patent/EP2259062A3/en
Priority to PT06255939T priority patent/PT1788391E/pt
Priority to DK06255939.8T priority patent/DK1788391T3/da
Priority to HK07109482.9A priority patent/HK1101765B/en
Assigned to UNIVERSAL BIOSENSORS PTY LTD. reassignment UNIVERSAL BIOSENSORS PTY LTD. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: LIFESCAN, INC.
Priority to US12/563,091 priority patent/US9863942B2/en
Priority to CY20111100725T priority patent/CY1113686T1/el
Abandoned legal-status Critical Current

Links

Images

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • G01N33/54373—Apparatus specially adapted for solid-phase testing involving physiochemical end-point determination, e.g. wave-guides, FETS, gratings
    • G01N33/5438—Electrodes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54313—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals the carrier being characterised by its particulate form
    • G01N33/54326—Magnetic particles
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T29/00—Metal working
    • Y10T29/49—Method of mechanical manufacture
    • Y10T29/49002—Electrical device making
    • Y10T29/49117—Conductor or circuit manufacturing
    • Y10T29/49124—On flat or curved insulated base, e.g., printed circuit, etc.

Definitions

  • Immunoassays are generally classified into two categories: competition assays and sandwich assays.
  • competition assay the antigen in the test sample is mixed with an antigen-probe complex (commonly referred to as a reporter complex) and the mixture then competes for binding to the antibody.
  • the probe may be a radioisotope, a fluorophore, or a chromophore.
  • sandwich immunoassay the antigen in the test sample binds to the antibody and then a second antibody-probe complex binds to the antigen.
  • one or more washing steps are usually required. The washing steps introduce complexity into the assay procedure and can generate biohazardous liquid waste.
  • Immunoassays usually provide a user with either a qualitative result (e.g., a “yes/no answer”) obtained, most often by a simple visual detection (e.g., color change), or a quantitative result such as a concentration of an antigen.
  • a qualitative result e.g., a “yes/no answer”
  • a simple visual detection e.g., color change
  • a quantitative result such as a concentration of an antigen.
  • Most of the quantitative methods involve expensive pieces of equipment, such as scintillation counters (for monitoring radioactivity), spectrophotometers, spectrofluorimeters (see, e.g., U.S. Pat. No. 5,156,972), surface plasmon resonance instruments (see, e.g., U.S. Pat. No. 5,965,456), and the like.
  • a disposable assay device for use in detecting a target analyte in a fluid sample, the device including a reaction chamber with an immobilized binding target and a probe conjugate positioned therein.
  • a binding reaction occurs between the immobilized binding target, probe conjugate, and/or target analyte (if present).
  • the target analyte if it is present, it causes a change in the amount of probe conjugate that is bound to the immobilized binding site. This change can be detected in a detection chamber.
  • the immobilized binding target, probe conjugate, and target analyte can include the variety of known ligands.
  • the immobilized binding target, probe conjugate, and target analyte can include an antigen or antibody, a hormone or neurotransmitter and a receptor, a substrate or allosteric effector and an enzyme, lectins and surgars, DNA or RNA structures, such as aptamers and their binding species (including other DNA or RNA species or binding protein), proteins, biotin and adivin or streptavidin systems, enzymes and their substrates and inhibitors, lipid binding systems, and combinations thereof.
  • immunological ligands will be described henceforth and the device will be referred to as an immunosensor or a biosensor.
  • the detection chamber mentioned above includes electrodes and electrochemical reagents.
  • an electrochemical reaction in the detection chamber can be used to determine if the amount of probe conjugate bound in the reaction chamber has been increased or reduced by the presence of the target antigen.
  • the electrochemical reaction can also be used to determine the analyte (e.g., target antigen) concentration based on the concentration of the probe conjugate in the detection chamber.
  • the immobilized binding site includes an antibody adapted to bind to a target antigen and the probe conjugate includes an antibody adapted to bind to a bound target antigen. If a target antigen is present in a fluid sample, the immobilized binding site can bind to one site on the target antigen, and the probe conjugate can bind to another site on the target antigen. The presence of a target antigen in the fluid sample thus results in an increase in the amount of probe bound in the reaction chamber and a reduction in the amount of probe conjugate in the detection chamber.
  • the immobilized binding site includes a target antigen and the probe conjugate includes an antibody adapted to bind to the target antigen.
  • a target antigen When a sample is introduced into the reaction chamber, a target antigen, if present, will bind with the probe conjugate.
  • the presence of a target antigen in the fluid sample results in a reduction in the amount of probe conjugate bound to the immobilized binding site in the reaction chamber and an increase in the amount of unbound probe conjugate that can travel to a detection chamber.
  • the reduction in bound probe conjugate can be detected and/or quantified by an electrochemical reaction in the detection chamber.
  • the immobilized binding site can include an antibody and the probe conjugate can include the target antigen. The presence of target antigen in the fluid sample will similarly cause a reduction in the amount of bound probe conjugate in the reaction chamber.
  • the immobilized binding sites and the probe conjugate are intermixed in the reaction chamber.
  • the immobilized binding sites and the probe conjugate are positioned separately.
  • immobilized binding sites can be located on magnetic beads that are dried on a surface of the reaction chamber. When a liquid sample is introduced into the reaction chamber, a magnetic field can be used to keep the magnetic beads and immobilized binding sites from moving into the detection chamber.
  • a method of detecting a target antigen in a fluid sample can include the steps of delivering a sample to an biosensor device that includes a reaction chamber and a detection chamber.
  • the sample is allowed to react with immobilized binding sites and a probe conjugate positioned within the reaction chamber.
  • the sample is then moved to a detection chamber, and the method further comprises the step of electrochemically detecting the probe conjugate in the detection chamber.
  • the detection step allows a user to determine if the target antigen is present in the sample based on the level of probe conjugate detected in the detection chamber.
  • the method can also include the step of quantifying the amount of target antigen in the sample based on electrical signals received from the detection chamber.
  • FIG. 1 is a top view of one embodiment of an biosensor disclosed herein;
  • FIG. 2 is a cross-sectional view of the biosensor of FIG. 1 along line A-A′;
  • FIG. 3 is a top view of another embodiment of a biosensor disclosed herein;
  • FIG. 4A is a cross-sectional view of the biosensor of FIG. 3 along the line A-A′;
  • FIG. 4B is a cross-sectional view of the biosensor of FIG. 3 along the line B-B′;
  • FIG. 4C is a cross-sectional view of the biosensor of FIG. 3 along the line C-C′;
  • FIG. 4D is a cross-sectional view of the biosensor of FIG. 3 along the line D-D′.
  • the senor includes a reaction chamber and a detection chamber. Positioned within the reaction chamber are immobilized binding sites that bind to the analyte of interest or to species related to the analyte of interest. Also in this chamber is a probe species that can be detected in the detection chamber, and which can be conjugated to a species that can bind to the immobilized binding site, or which can bind to a species that binds to the immobilized binding site. This will be hereafter termed the probe conjugate.
  • the probe conjugate and the immobilized binding site are such that the presence of the analyte of interest in the sample modifies the interaction of the probe conjugate and the immobilized binding site.
  • the analyte when present, can block the probe conjugate from binding to the immobilized binding site.
  • the analyte can provide a site for the probe conjugate to bind, thereby increasing the amount of bound probe conjugate.
  • the presence of analyte modifies the amount of the probe conjugate bound in the reaction chamber.
  • the reaction chamber can be arranged so that after the probe conjugate binding reactions have taken place to the desired extent, the liquid from the reaction chamber is transferred to the detection chamber, transferring with it the free probe conjugate and leaving behind the bound probe conjugate.
  • the amount of free probe conjugate can be detected.
  • electrodes in the detection chamber can be used to electrochemically detect the level of probe conjugate in the detection chamber.
  • the electrochemical reaction can determine if the target analyte is present/absent and/or determine the concentration of the target analyte based on the amount of the probe conjugate in the detection chamber.
  • a first embodiment of a biosensor 20 includes a detection chamber 28 comprising an electrochemical cell and a reaction chamber 22 containing immobilized binding sites and a probe conjugate.
  • the detection chamber 28 and reaction chamber 22 can be prepared by forming an aperture extending through a sheet of electrically resistive spacer material 36 .
  • the aperture can be shaped such that it defines a sidewall of both the reaction chamber 22 and detection chamber 28 , as well as a sample passageway 38 between chambers 22 , 28 .
  • a sample ingress 25 is also formed.
  • the thickness of sheet 36 defines the height of the reaction chamber 22 and detection chamber 28 , and the chambers can have an equal height.
  • the capillary force in the detection chamber must be greater than that in the reaction chamber. This can be achieved by modifying the surfaces of the reaction chamber and/or detection chamber or by adding filling materials, such as those herein disclosed, to the detection chamber.
  • the height of reaction chamber 22 is greater than that of detection chamber 28 .
  • a reaction chamber 22 of greater height than detection chamber 28 can be prepared, for example, by layering multiple inner sheets 32 , 34 , 36 and/or outer sealing sheets 42 , 46 together.
  • the middle sheet 36 of sensor 20 has an aperture defining the sidewalls of reaction chamber 22 and detection chamber 28 as described above.
  • Middle sheet 36 is then sandwiched between one or more additional layers 32 , 34 , the additional layers 32 and 34 having an aperture corresponding only to reaction chamber 22 .
  • layers 32 and 34 define the end walls 60 , 62 (i.e., top and bottom surfaces) of the chamber.
  • the end walls 60 and 62 of the detection chamber comprise electrodes 54 and 52 , electrically connectable, via connection means, to a measuring circuit. The electrodes are described in more detail below.
  • the electrodes 52 and 54 can be placed in electrical connection with a meter (not shown) through the connection end 66 .
  • the connection end allows a meter (not shown) to electrically communicate with the electrodes 52 and 54 in the detection chamber 28 via electrically conductive tracks (not shown).
  • the meter in connection with the connection area 66 is capable of applying a potential between the electrodes 52 and 54 in the detection chamber 28 and detecting the electrical signals generated during an electrochemical reaction.
  • a user first introduces sample into the first chamber, the reaction chamber 22 , of the sensor through sample ingress 25 .
  • the sample can be drawn into the reaction chamber under the influence of capillary or wicking action.
  • the reaction chamber can include a vent 26 that is open to the atmosphere, thus allowing air displaced by the sample to escape. Sample will be drawn into the first chamber until it is filled up to the reaction chamber vent 26 , whereupon filling will stop.
  • the volume of reaction chamber 22 is chosen so as to be at least equal to and preferably larger than the volume of the detection chamber 28 .
  • the dashed circle in FIG. 1 denotes an aperture 30 piercing layers 32 , 34 , and/or 36 but not layers 42 and 46 . Since layers 42 and 46 are not pierced initially, the only opening to the atmosphere of the detection chamber 28 is through sample passageway 38 that opens from reaction chamber 22 . Thus, when reaction chamber 22 fills with sample, air is trapped in detection chamber 28 , which substantially prevents it from filling with sample. A small amount of sample can enter the detection chamber 28 during the time between when the sample first contacts the opening 38 to the detection chamber 28 and when it contacts the far side of the opening 38 . However, once the sample has wet totally across the opening 38 to the detection chamber 28 , no more filling of detection chamber 28 will take place.
  • Vent 56 can be opened in a variety of ways, including, for example, by puncturing an outer layer of the device, by removing a portion of the outer layer of the device, and/or by tearing away a portion of the device.
  • the reacted sample When the vent is opened, the reacted sample will be drawn into the detection chamber 28 due to increased capillary force in the detection chamber 28 compared to that present in the reaction chamber 22 .
  • the increased capillary force is provided by suitably coating the surfaces of the detection chamber 28 or, more preferably, by choosing the capillary distance for detection chamber 28 to be smaller than that of reaction chamber 22 .
  • the capillary distance is defined to be the smallest dimension of the chamber.
  • the capillary forces in the reaction and/or detection chambers can be created by varying a number of factors. Capillary forces in thin chambers are discussed, for example, in U.S. Pat. No. 6,823,750, entitled “Method of Preventing of Preventing Short Sampling of a Capillary or Wicking Fill Device,” which is hereby incorporated by reference in its entirety.
  • FIGS. 3 through 4 D A second exemplary embodiment of a biosensor 120 , including three chambers, is illustrated in FIGS. 3 through 4 D.
  • the immunosensor can include a filling chamber 107 in addition to a reaction chamber 122 and a detection chamber 128 .
  • Sensor 120 can be formed from multiple layers as described above, including for example, a sealing layer 142 , a lower layer 134 , a spacer layer 136 , and an upper layer 132 .
  • each layer comprises an insulating material, while upper and lower layers 132 , 134 additionally include an electrically conductive film as discussed in more detail below.
  • exposing portions of the electrically conductive film on the upper and lower layers 132 , 134 provides electrodes 152 , 154 for performing electrochemical reactions and provides electrical contact areas 101 , 102 , 103 for electrically connecting the sensor to a meter.
  • Filling chamber 107 receives the sample from the patient or user and provides a reservoir of sample for filling the other two chambers.
  • Reaction chamber 122 and detection chamber 128 are in fluid communication with filling chamber 107 .
  • detection chamber 128 can include vent 130 which is initially closed. After a sample is reacted in the reaction chamber, vent 130 is opened so that air in detection chamber 128 can exit through the vent allowing liquid from reaction chamber 122 to enter the detection chamber.
  • vent 130 can be opened in a variety of ways, including piercing the device, removing an outer layer, and/or tearing a portion of the device (i.e., tearing along a perforation).
  • the sensor can include electrical connection point 101 that allows an electrical connection to be made to a lower electrode 152 and electrical connection points 102 , 103 that allow an electrical connection to an upper electrode 154 .
  • Dotted line 106 denotes a break in the electrically conductive film defining upper electrode 154 on upper layer 132 .
  • the break may be affected by patterning the conductive film when it is laid down or by creating the break during manufacture. The break could be affected by scratching the film, scraping part of the film away, chemically etching the film, laser ablating the film or other methods as commonly known.
  • Break 106 in the conductive film serves to, in part, define the active electrode area of the strip by electrically isolating the conductive coated in the detection chamber from that in the reaction chamber. This is advantageous as it can prevent any electric signal that might otherwise flow at the conductive films in the reaction chamber from effecting the test results.
  • Sensor 120 can also include contact point 103 which allows a user to electrically connect to the portion of conductive film in contact with reaction chamber 122 .
  • monitoring contact point 103 allows a signal to be detected that indicates to the meter that the strip has been successfully filled and a test sequence can commence.
  • an electrical connection could be made to the lower conductive film at contact point 101 and to the upper conductive film in the reaction chamber at contact point 103 .
  • a potential would then be applied between the two connection points ( 101 , 103 ) and the current, voltage, and/or electrical resistance monitored to ascertain when sample has entered the reaction chamber.
  • This potential may be a DC potential or it may be a potential that varies with time such as an AC potential or a series of square wave potential pulses with alternating polarity.
  • Connection area 101 for electrically contacting a lower layer 134 carrying the lower conductive film, can be formed by extending lower layer 134 out past the end of a spacer layer 136 and the upper layer 132 .
  • Contact area 102 is formed by removing sections of layers 134 and 136 to expose a section of upper layer 132 .
  • Contact area 103 is similarly formed by removing a section of lower layer 134 and spacer layer 136 as shown in FIG. 4D (cross-section D-D′ In FIG. 3 ).
  • Filling chamber 107 can be formed by removing sections of lower layer 134 and spacer layer 136 , but leaving upper layer 132 and sealing layer 142 intact. Sealing layer 142 can be adhered to the outside face of layer 134 and can serve, with the sides of the cut-out sections in layers 134 and 136 and layer 132 , to form a capillary channel which is capable of drawing sample into it by capillary action. This channel is illustrated in FIG. 4A (cross-section A-A′ in FIG. 3 ).
  • Reaction chamber 122 is formed by removing a section of the spacer layer 136 but leaving layers 134 and 132 intact. This forms a capillary space where the height of the capillary spacer is smaller than the height of the filling chamber 122 . This allows capillary forces to draw liquid from the filling chamber 122 into the reaction chamber 128 by capillary action. The small height of the reaction chamber can also allow for relatively rapid mixing of components in the reaction chamber.
  • reaction chamber 122 opens at the lateral edge(s) of the strip to allow air to vent while liquid fills the reaction chamber.
  • Detection chamber 128 is formed in a similar fashion to the reaction chamber 122 by removing a section of the spacer layer 136 while leaving the layers 134 and 132 intact. Initially, the detection chamber 128 opens to the reaction chamber 122 at one end but has no other opening.
  • Vent hole 130 is incorporated into the detection chamber 128 by removing sections of or piercing upper layer 132 (or lower layer 134 ).
  • a layer 146 shown in FIG. 4B can be laminated to the upper face of the strip to seal off the opening.
  • sealing layer 142 can be pierced/removed to open vent hole 130 .
  • the immunosensor described herein can have a variety of alternative configurations such as, for example, the shape of the sensor, the number of chambers, the electrode configuration, and/or the placement of electrical contact points.
  • other sensor devices that are illustrative of a variety of alternative sensor embodiments are disclosed in a U.S. application entitled “Method and Apparatus for Electrochemical Analysis,” filed concurrently herewith and incorporated by reference in its entirety.
  • vents to control the flow of fluid between chambers
  • other fluid directing embodiments are also contemplated.
  • a physical barrier between the reaction chamber and the detection chamber could be removed or opened to permit the flow of fluid between chambers.
  • the sensors described herein could also include pumping elements to move fluids through the device.
  • the immunosensor of the present invention includes electrodes 52 , 152 and 54 , 154 as described above.
  • an electrode configuration other than the opposing relationship illustrated in the FIGS. may be used, for example, a side-by-side relationship, or an offset relationship.
  • the electrodes may be identical or substantially similar in size, or may be of different sizes and/or different shapes.
  • the electrodes may comprise the same conductive material, or different materials. Other variations in electrode configuration, spacing, and construction or fabrication will be apparent to those of skill in the art.
  • the electrodes are mounted in a parallel opposing relationship at a distance of less than or equal to 500, 450, 400, 350, 300, 250, or 200 microns, and more preferably from about 5, 10, 15, 20, 25, 30, 35, 40, 45, or 50 microns to about 75, 100, 125, 150, or 175 microns. In certain embodiments, however, it may be preferred that the electrode spacing is greater than 500 microns, for example, 600, 700, 800, 900, or 1000 microns, or even greater than 1, 2, 3, 4, or 5 millimeters.
  • At least one of the electrodes can be a sensing electrode, i.e., an electrode sensitive to the amount of reduced redox agent in the antioxidant case or oxidized redox agent in the oxidant case.
  • a sensing electrode i.e., an electrode sensitive to the amount of reduced redox agent in the antioxidant case or oxidized redox agent in the oxidant case.
  • a second electrode acting as reference electrode is present which acts to provide a reference potential.
  • at least one other electrode is present which functions as a counter electrode to complete the electrical circuit.
  • This second electrode may also function as a reference electrode.
  • an additional electrode (not shown) may perform the function of a reference electrode.
  • the electrically conductive film defining electrodes 52 , 152 , 54 , 154 can be adhered to a surface the immunosensor by means of an adhesive.
  • Suitable adhesives include, for example, heat activated adhesives, pressure sensitive adhesives, heat cured adhesives, chemically cured adhesives, hot melt adhesives, hot flow adhesives, and the like.
  • the electrically conductive film is prepared by coating (e.g., by sputter coating or screen printing) a sheet of electrically resistive material with a suitable electrically conductive material, for example, platinum, palladium, carbon, indium oxide; tin oxide, mixed indium/tin oxides, gold, silver, iridium, mixtures thereof, and the like.
  • Suitable electrically resistive materials include, for example, polyesters, polystyrenes, polycarbonates, polyolefins, mixtures thereof, and the like.
  • Reagents for use in the immunosensor may be supported on the walls the reaction chamber 22 , 122 or on an independent support contained within chambers, within a matrix, or may be self supporting. If the reagents are to be supported on the chamber walls or the electrodes, the chemicals can be applied by use of printing techniques well known in the art, e.g., ink jet printing, screen printing, lithography, and the like. In an alternative embodiment, a solution containing the reagent is applied to a surface within a chamber and allowed to dry.
  • immunological species and/or electrochemical reagents can be supported on and/or contained within one or more independent supports which are placed into the sensor.
  • Suitable independent supports include, but are not limited to, mesh materials, nonwoven sheet materials, fibrous filling materials, macroporous membranes, sintered powders, and/or beads.
  • the advantages of independent supports include an increased surface area, thus allowing more immobilized binding sites and probe conjugate to be included in the reaction chamber 22 , 122 .
  • an immobilized antibody and/or probe conjugate are dried onto support materials, which are then placed into the reaction chamber.
  • either the immobilized binding site or probe conjugate is incorporated onto a support material and the other component is supported on the reaction chamber wall.
  • the walls of the reaction chamber are porous, with the immobilized binding site and/or probe conjugate incorporated therein. This can be accomplished by using a macroporous membrane to form the reaction chamber wall and compressing the membrane around the reaction chamber to prevent leakage of sample out of the desired area.
  • Suitable independent supports include material such as mesh materials, nonwoven sheet materials, and fibrous fill materials include, polyolefins, polyesters, nylons, cellulose, polystyrenes, polycarbonates, polysulfones, mixtures thereof, and the like.
  • Suitable macroporous membranes may be prepared from polymeric materials including polysulfones, polyvinylidene difluorides, nylons, cellulose acetates, polymethacrylates, polyacrylates, mixtures thereof, and the like.
  • the immobilized binding site and/or probe conjugate is supported on beads.
  • Such beads may comprise a polymeric material, e.g., agarose, polystyrene, polymethacrylate, polymethylmethacrylate, optionally encasing a magnetic material (such as gamma Fe 2 O 3 and Fe 3 O 4 ).
  • the bead material is selected such that suitable support for the antibody is provided.
  • Suitable beads may include those marketed as DYNABEADS® by Dynal Biotech of Oslo, Norway.
  • a magnet may be included to hold the magnetic beads in the reaction chamber and to stop them from moving to the detection chamber.
  • the immobilized biding site can be positioned on magnetic beads within the reaction chamber.
  • sensor 20 , 120 can include an immobilized binding site and a probe conjugate. While the following description is made with respect to sensor 20 of FIG. 2 , it will be apparent that it applies to sensor 120 as well.
  • an immobilized binding site 44 is an antibody to the antigen to be detected and the probe conjugate 50 is an enzyme linked to the antigen to be detected or a pseudo-antigen of the antigen to be detected.
  • the antibodies 44 can be adsorbed or otherwise immobilized therein such that they do not move from the reaction chamber during a test.
  • an agent designed to prevent non-specific binding of proteins to this surface can be applied (not shown).
  • An example of such an agent well known in the art is bovine serum albumin (BSA).
  • BSA bovine serum albumin
  • a nonionic surfactant may also be used as such an agent, e.g., TRITON X100 manufactured by Rohm & Haas of Philadelphia, Pa., or TWEEN manufactured by ICI Americas of Wilmington, Del.
  • the nonionic surfactant selected does not denature proteins.
  • probe conjugate 50 Spaced apart from the antibodies is probe conjugate 50 (enzyme-linked antigen).
  • suitable enzymes for use with probe conjugate 50 include, but are not limited to, glucose oxidase and glucose dehydrogenase.
  • the enzyme-linked antigen 50 can be deposited within the reaction chamber in such a way that it can be liberated into the sample when wetted by the sample.
  • the enzyme-linked antigen 50 can be dried on a surface within the reaction chamber, such that only a weak bond between the enzyme-linked antigen 50 and the reaction chamber exists.
  • the rate of dissolution of the enzyme-linked antigen 50 is chosen such that probe conjugate will dissolve in a sample during the time taken for the sample to fill the reaction chamber. In this manner, the enzyme-linked antigen 50 can be evenly distributed throughout the area of the reaction chamber after filling.
  • the relative amounts of enzyme-linked antigen 50 and antibody 44 can be chosen such that there is an excess of antibody 44 over enzyme-linked antigen 50 .
  • an excess is defined to be such that the excess is small when compared to the number of antigen molecules to be detected in the sample.
  • the enzyme-linked antigen 50 mixes with the sample. Sufficient time is then allowed for the enzyme-linked antigen 50 to come into contact with the antibodies 44 . Since there is an excess of antibodies 44 , if no antigen is present in the sample then substantially all, or a large portion, of the enzyme-linked antigen 50 will bind to the antibodies 44 and so be effectively immobilized. If target antigen is present in the sample, the target antigen will contact and bind to the antibodies 44 , blocking at least some of the enzyme-linked antigen 50 from binding with the antibodies 44 .
  • the enzyme-linked antigen 50 (or at least a measurable portion thereof) will remain mobile in the sample and can move into the detection chamber. Conversely, if no target antigen is present in the sample, then the enzyme-linked antigen 50 will be immobilized in 48 reaction chamber (or at least a measurable reduction in the amount remaining mobile in the sample).
  • an excess of antibody 44 is not necessary and that alternatively, the relative amounts of enzyme-linked antigen 50 and antibody 44 can be equal, or an excess of enzyme-linked antigen 50 can be present.
  • the immobilized binding site 44 is an antibody that can bind to a site on the target antigen and the probe conjugate 50 includes an enzyme coupled to an antibody that can bind to bound target antigen.
  • the immobilized binding site in the reaction chamber can bind to one site on the analyte of interest.
  • the probe conjugate can include a second antibody that can bind to a second site on the target antigen attached to the immobilized binding site.
  • the probe conjugate and the immobilized binding site mix with the sample and the analyte of interest binds at one site to the probe conjugate and at a second site to the immobilized binding site.
  • the analyte therefore forms a link that immobilizes a fraction of the probe conjugate, where the fraction immobilized can be used to detect the presence and/or quantify the concentration of the analyte in the sample.
  • the amount of immobilized probe conjugate can be quantified by observing the drop in the amount of free probe conjugate that is transferred to the detection chamber.
  • the immobilized binding site 44 can be the target antigen and the probe conjugate 50 can comprise an enzyme coupled to an antibody that is capable of binding to the analyte of interest.
  • the immobilized binding site and probe conjugate are position separately in the reaction chamber to prevent or reduce any reaction prior to the introduction of sample.
  • the target antigen in the sample can bind to the probe conjugate (antibody), reducing the amount of probe conjugate that binds to the immobilized binding site (antigen).
  • the presence or absence of the target antigen therefore changes the amount of probe conjugate bound in the reaction chamber.
  • the fraction immobilized can be used to detect the presence and/or quantify the concentration of the analyte in the sample. For example, the amount of immobilized probe conjugate can be quantified by observing the drop in the amount of free probe conjugate that is transferred to the detection chamber.
  • the immobilized binding sites and/or the probe conjugate are bound to beads.
  • the immobilized binding sites (antigen) can be positioned on beads that are dried on one surface of the reaction chamber and the probe conjugate (antibody) can be dried on another surface of the reaction chamber.
  • the beads can be magnetic beads that are prevented from leaving the reaction chamber by means of a magnetic field.
  • beads can have characteristics such that they will remain in the reaction chamber when the sample transfers to the detection chamber.
  • the para-magnetic beads can be aligned with field lines of an applied magnetic field such that they are held by the field and thus prevented from being transferred with the sample to detection chamber.
  • the magnetic field can be applied by any suitable device such as an electromagnet or, in an alternative embodiment when it is desired to minimize power consumption, the magnetic field can be applied by a permanent magnet.
  • the magnet or magnets could be placed so that they are closer to the location in the reaction chamber of the probe conjugate and further from the location in the reaction chamber of the para-magnetic beads. With this arrangement, the beads will tend to move towards, and mix with, the probe conjugate under the influence of the magnetic field. Once the beads have moved to and mixed with the probe conjugate, the applied magnetic field will tend to prevent the beads from moving to locations with a lower concentration of magnetic field lines, thus the beads will be immobilized in the reaction chamber by the magnetic field.
  • the reacted sample is moved to the detection chamber. This can occur at a predetermined time after the sample is introduced into the reaction chamber.
  • the predetermined time can be set such that there is sufficient time for substantially all of the probe conjugate to bind.
  • the residence time of the sample in the reaction chamber can be calculated by a user manually. Alternatively, the residence time can be calculated electronically by a meter in electrical contact with the sensor.
  • the residence time of the sample in the reaction chamber is monitored via electrodes.
  • electrodes For example, in the sensor of FIGS. 1 and 2 when sample fills the reaction chamber 22 , a small portion of the detection chamber 28 at its opening 38 into the reaction chamber 22 will be wet by sample.
  • the electrodes 52 and 54 can be placed in the detection chamber 28 , such that at least a portion of each electrode 52 and 54 is contacted by the sample during the filling of the reaction chamber 22 , such that the presence of the sample will bridge the electrodes 52 and 54 and create an electrical signal which can be used to trigger the timing device.
  • a separate electrically contact (contact 103 ), used in conjunction with the lower electrode and contact area 101 , can detect the presence of sample in the reaction chamber.
  • the immunological reaction phase of the test is deemed to be completed.
  • the vent 30 , 130 can then be opened to the atmosphere.
  • a solenoid activated needle in the meter may be used to pierce layer the vent.
  • the piercing can be automatically performed by the meter or manually by the user, e.g., the user inserts a needle through the layer(s) covering the vent.
  • the detection chamber 28 , 128 are dried reagents 64 comprising an enzyme substrate and a mediator, capable of reacting with the enzyme part of the probe conjugate to produce a detectable signal.
  • the enzyme substrate and mediator can be of sufficient amount such that the rate of reaction of any enzyme present with the enzyme substrate is determined by the amount of enzyme present. For instance, if the enzyme were glucose oxidase or glucose dehydrogenase, a suitable enzyme mediator and an enzyme substrate such as glucose (if not already present in the sample) would be disposed into detection chamber 28 , 128 . In one alternative embodiment sufficient glucose would be disposed into the detection chamber 28 , 128 such that any variations in the level of glucose in the incoming sample did not significantly alter the enzyme reaction rate.
  • Buffer may also be included to help adjust the pH of the sample in detection chamber 28 , 128 .
  • ferricyanide is a suitable mediator.
  • suitable mediators include dichlorophenolindophenol and complexes between transition metals and nitrogen-containing heteroatomic species.
  • a second mediator such as phenazine ethosulphate, and/or 2,3 dimethoxy-5-methy-p-benzoquinone, which promotes a more efficient transfer of electrons from the enzyme to the ferricicyanide species can be added.
  • the enzyme substrate, mediator, second mediator, and buffer reagents 64 can be present in sufficient quantities such that the rate of reaction of the enzyme with the enzyme substrate is limited by the concentration of the enzyme present.
  • the reagents 64 dissolve into the sample.
  • the enzyme component of the probe conjugate reacts with the enzyme substrate and the mediator to produce reduced mediator.
  • This reduced mediator is electrochemically oxidized at an electrode acting as an anode in the detection chamber 28 , 128 to produce an electrical current.
  • the rate of change of this current with time is used as an indicator of the presence and amount of enzyme that is present in the reacted sample. If the rate of change of current is less than (or more than) a predetermined threshold value, then it indicates that no significant amount (or a significant amount) of probe conjugate 50 is present in the reacted sample, indicating the presence (or lack) of antigen present in the original sample.
  • the rate of change of a current more than (or less than) a predetermined threshold value can be used to indicate the lack (or presence) of an antigen in the sample.
  • the rate of change of the current is used to give a measure of the relative amount of antigen initially present in the sample.
  • the rate of change of current can be used to determine probe conjugate concentration, which can be correlated to the concentration of the antigen in the sample.
  • a probe-linked antigen comprising an antigen-melittin complex can be dried on a wall of the reaction chamber, as described above.
  • the detection chamber can contain a mediator comprising ferrocyanide in liposomes or lipid vesicles. If the antigen-melittin complex reaches the liposomes, they will burst and release the ferrocyanide. This leads to a rapid amplification of the signal, i.e., a small amount of free antigen competes with the antigen-melittin complex for binding sites on the antibodies and results in a large concentration of ferrocyanide.
  • HRP horse radish peroxidase
  • AP alkaline phosphatase
  • substrates have been developed which allow both these enzymes to be used in an electrochemical assay.
  • AP can be used with p-aminophenyl phosphate
  • HRP can be used with tetrathiafulvalene.
  • C reactive protein was covalently attached to 1.5 micron Carboxylated BioMag magnetic beads (Cat no BM570; Bangs Laboratories, Indianapolis In, USA). 21.9 mg of beads (1 ml) were washed 4 times with 50 mM MES (Morpholinoethanesulphonic acid (Sigma-Aldrich, St Louis, Mo. USA) buffer pH 5.2 by incubating with this buffer and using a magnet to concentrate the beads on the side of the tube and after 2 min remove the buffer with a transfer pipette. After the fourth wash, the beads were suspended in a final volume of 0.34 ml 50 mM MES. 40 ul of 100 mg/ml EDAC (Sigma, St Louis, Mo.
  • MBS was reacted with amino groups on GDH and the MBS-GDH intermediate was purified. Then maleimide groups on the SMCC-GDH complex were reacted with free sulphydryl groups on the hinge region of the antibody introduced by reaction with the reducing reagent cysteamine HCl.
  • cysteamine HCl (Sigma-Adrich, St Louis, Mo. USA) was incubated for 90 minuets at 37° C. with 1 ml of a solution containing 2 mg/ml Mab C2 in a buffer containing 0.1M Sodium phosphate pH 7.4; 0.15 M NaCl and 2.5 mM EDTA (reaction buffer). The reaction was terminated by applying the mixture to a desalting column (PD-10; Amerscham) equilibrated in reaction buffer and elution continued in the same buffer. One-half milliliter fractions were collected and the three fractions containing the most protein were pooled. This material was reacted with the maleimide activated enzyme as soon as it was pooled. The protein concentration was determined assuming an absorbance at 280 nm of 1.35 for a 1 mg/ml solution of antibody C2.
  • the reduced IgG and maleimide reacted GDH were mixed together in the ratio of 1 mg of Ab to 0.9 mg of GDH and incubated overnight at 4° C.
  • the reaction was terminated by adding 6 mg of cysteamine HCl and allowing to incubate for a further 15 min at room temperature and then applying 1.5 ml aliquots to separate desalting columns equilibrated with and continuing the elution in a buffer containing 20 mM Tris and 0.15 M Sodium Chloride pH 7.4 (TBS).
  • TBS Sodium Chloride pH 7.4
  • the three 0.5 ml fractions containing the highest concentration of protein from each column were pooled.
  • Calcium chloride was added to a final concentration of 1 mM, sodium azide to a final concentration of 0.1% and PQQ to a final concentration of 0.05 mg/ml. Conjugate was stored at 4° C. prior to use.
  • the CRP levels in samples were also determined by conventional enzyme immunoassay. All incubations were carried out at room temperature.
  • TBS buffer containing 0.1% TWEEN 20 (Polyoxyethylenesorbitan monlaurate; Sigma-Adrich, St Louis, Mo. USA).
  • Biotinylation of antibody C6 was carried out by the following method. Two milligrams of monoclonal antibody C6 (Hytest, Turku Finland) were dissolved 1 ml of 50 mM Sodium bicarbonate and reacted with 29 ul of 1 mg/ml solution of biotin N Hydroxysuccinimide ester (Pierce) in Dimethyl sulphoxide (Sigma). The reaction was allowed to proceed for 30 min with occasional shaking.
  • the reaction was terminated by applying the mixture to a desalting column (PD-10; Amerscham) equilibrated in 20 mM Tris (2-amino-2-hydroxymethyl)-1,3 propandiol), 0.15 M Sodium Chloride pH 7.4 (TBS) and elution continued in the same buffer. One-half milliliter fractions were collected and the three fractions containing the most protein were pooled. The material was stored at 4° C. Protein concentration was determined by absorbance at 280 nm assuming a 1 mg/ml solution of C6 had an absorbance of 1.2.
  • the solution contained 5 mg/ml 2,3 Dimethoxy-5-methyl 1,4 benzoquinone (Adrich, Wis. USA) 326 mg/ml potassium ferricyanide 400 mM glucose in a buffer containing 0.26 mg/ml citraconic acid (Sigma) and 13.3 mg/ml Di potassium citraconate.
  • Solution contained 400 ug/ml GDH was diluted to 100 ug/ml in a solution containing 1 mM Calcium chloride, 10 mg/ml BSA 0.26 mg/ml citraconic acid, 13.3 mg/ml Di potassium citraconate, and 10 mg/ml sucrose.
  • Solution contained 5 mg/ml CRP coated beads, 100 mg/ml sucrose, 1 mM Calcium chloride, 0.26 mg/ml citraconic acid, and 13.3 mg/ml Di potassium citraconate
  • the vent hole 130 in FIG. 3 was punctured. This allowed blood together with any unbound GDH conjugate to flow past the scratch line ( 106 ) into the detection chamber where measurement of the electrical current flowing between the electrodes in the detection chamber was initiated. The current generated by the presence of GDH in the detection chamber was measured over the next 45 s.
  • the results below are for six replicate samples of the control blood or blood containing 250 ug/ml CRP. They show the current in ⁇ A at 5 seconds and 45 seconds after the detection chamber 128 was filled. The difference in the current between 5 and 45 seconds was used as a measure of the CRP concentration in the sample.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Immunology (AREA)
  • Engineering & Computer Science (AREA)
  • Molecular Biology (AREA)
  • Biomedical Technology (AREA)
  • Chemical & Material Sciences (AREA)
  • Hematology (AREA)
  • Urology & Nephrology (AREA)
  • Food Science & Technology (AREA)
  • Biochemistry (AREA)
  • Cell Biology (AREA)
  • Biotechnology (AREA)
  • Medicinal Chemistry (AREA)
  • Physics & Mathematics (AREA)
  • Analytical Chemistry (AREA)
  • Microbiology (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Pathology (AREA)
  • Apparatus Associated With Microorganisms And Enzymes (AREA)
  • Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
  • Investigating Or Analysing Biological Materials (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
US11/284,097 2002-03-21 2005-11-21 Biosensor apparatus and methods of use Abandoned US20060134713A1 (en)

Priority Applications (14)

Application Number Priority Date Filing Date Title
US11/284,097 US20060134713A1 (en) 2002-03-21 2005-11-21 Biosensor apparatus and methods of use
JP2006312451A JP5288700B2 (ja) 2005-11-21 2006-11-20 バイオセンサー装置及びその使用方法
ES06255939T ES2365169T3 (es) 2005-11-21 2006-11-21 Aparato biosensor y procedimientos de uso.
CNA2006101493105A CN1975421A (zh) 2005-11-21 2006-11-21 生物传感器设备及使用方法
SI200631079T SI1788391T1 (sl) 2005-11-21 2006-11-21 Biosenzorski aparat in postopki uporabe
PT06255939T PT1788391E (pt) 2005-11-21 2006-11-21 Dispositivo biossensor e métodos de utilização
DK06255939.8T DK1788391T3 (da) 2005-11-21 2006-11-21 Biosensorindretning og fremgangsmåder til brug deraf
EP10179412A EP2259062A3 (en) 2005-11-21 2006-11-21 Biosensor apparatus and methods of use
EP06255939A EP1788391B1 (en) 2005-11-21 2006-11-21 Biosensor apparatus and methods of use
AT06255939T ATE509274T1 (de) 2005-11-21 2006-11-21 Biosensorvorrichtung und verfahren zu ihrer verwendung
PL06255939T PL1788391T3 (pl) 2005-11-21 2006-11-21 Czujnik biologiczny i sposoby zastosowania
HK07109482.9A HK1101765B (en) 2005-11-21 2007-08-31 Biosensor apparatus and methods of use
US12/563,091 US9863942B2 (en) 2002-03-21 2009-09-18 Biosensor apparatus and methods of use
CY20111100725T CY1113686T1 (el) 2005-11-21 2011-07-22 Συσκευη bio-αισθητηρα και οι μεθοδοι χρησης της

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US10/105,050 US20030180814A1 (en) 2002-03-21 2002-03-21 Direct immunosensor assay
US10/830,841 US8685714B2 (en) 2000-07-14 2004-04-22 Immunosensor
US11/284,097 US20060134713A1 (en) 2002-03-21 2005-11-21 Biosensor apparatus and methods of use

Related Parent Applications (2)

Application Number Title Priority Date Filing Date
US10/105,050 Continuation-In-Part US20030180814A1 (en) 2002-03-21 2002-03-21 Direct immunosensor assay
US10/830,841 Continuation-In-Part US8685714B2 (en) 2000-07-14 2004-04-22 Immunosensor

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US12/563,091 Division US9863942B2 (en) 2002-03-21 2009-09-18 Biosensor apparatus and methods of use

Publications (1)

Publication Number Publication Date
US20060134713A1 true US20060134713A1 (en) 2006-06-22

Family

ID=37762369

Family Applications (2)

Application Number Title Priority Date Filing Date
US11/284,097 Abandoned US20060134713A1 (en) 2002-03-21 2005-11-21 Biosensor apparatus and methods of use
US12/563,091 Expired - Lifetime US9863942B2 (en) 2002-03-21 2009-09-18 Biosensor apparatus and methods of use

Family Applications After (1)

Application Number Title Priority Date Filing Date
US12/563,091 Expired - Lifetime US9863942B2 (en) 2002-03-21 2009-09-18 Biosensor apparatus and methods of use

Country Status (11)

Country Link
US (2) US20060134713A1 (pl)
EP (2) EP1788391B1 (pl)
JP (1) JP5288700B2 (pl)
CN (1) CN1975421A (pl)
AT (1) ATE509274T1 (pl)
CY (1) CY1113686T1 (pl)
DK (1) DK1788391T3 (pl)
ES (1) ES2365169T3 (pl)
PL (1) PL1788391T3 (pl)
PT (1) PT1788391E (pl)
SI (1) SI1788391T1 (pl)

Cited By (137)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040137141A1 (en) * 2001-11-28 2004-07-15 Dick Kenneth W. Solution drying system
US20050180971A1 (en) * 2002-02-14 2005-08-18 Ashdown Martin L. Cancer therapy
US20060266644A1 (en) * 2005-05-25 2006-11-30 Lifescan, Inc. Method and apparatus for electrochemical analysis
US20070202119A1 (en) * 2003-10-24 2007-08-30 Ashdown Martin L Method Of Therapy
US20070205103A1 (en) * 2005-05-25 2007-09-06 Lifescan, Inc. Method and apparatus for electrochemical analysis
US7297151B2 (en) 2002-04-19 2007-11-20 Elikan Technologies, Inc. Method and apparatus for body fluid sampling with improved sensing
US7316700B2 (en) 2001-06-12 2008-01-08 Pelikan Technologies, Inc. Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties
US7344894B2 (en) 2001-10-16 2008-03-18 Agilent Technologies, Inc. Thermal regulation of fluidic samples within a diagnostic cartridge
US7344507B2 (en) 2002-04-19 2008-03-18 Pelikan Technologies, Inc. Method and apparatus for lancet actuation
US7374544B2 (en) 2002-04-19 2008-05-20 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7410468B2 (en) 2002-04-19 2008-08-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US20080248022A1 (en) * 2004-09-08 2008-10-09 Immunaid Pty Ltd Therapeutic Strategy for Treating Autoimmune and Degenerative Diseases
US7481776B2 (en) 2002-04-19 2009-01-27 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
WO2009018348A1 (en) * 2007-07-30 2009-02-05 Cornell Research Foundation, Inc. Microchannel detection device and use thereof
US20090041760A1 (en) * 2000-08-18 2009-02-12 Martin Leonard Ashdown Retroviral immunotherapy
US7491178B2 (en) 2002-04-19 2009-02-17 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7524293B2 (en) 2002-04-19 2009-04-28 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7537571B2 (en) 2001-06-12 2009-05-26 Pelikan Technologies, Inc. Integrated blood sampling analysis system with multi-use sampling module
US7547287B2 (en) 2002-04-19 2009-06-16 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7563232B2 (en) 2002-04-19 2009-07-21 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7582099B2 (en) 2002-04-19 2009-09-01 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US7582063B2 (en) 2000-11-21 2009-09-01 Pelikan Technologies, Inc. Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means
US7604592B2 (en) 2003-06-13 2009-10-20 Pelikan Technologies, Inc. Method and apparatus for a point of care device
US20090305431A1 (en) * 2006-02-21 2009-12-10 Universal Biosensors Pty Ltd. Fluid transfer mechanism
US7648468B2 (en) 2002-04-19 2010-01-19 Pelikon Technologies, Inc. Method and apparatus for penetrating tissue
US7666149B2 (en) 1997-12-04 2010-02-23 Peliken Technologies, Inc. Cassette of lancet cartridges for sampling blood
WO2010004436A3 (en) * 2008-07-11 2010-02-25 University Biosensors Pty Ltd. Enhanced immunoassay sensor
US7674232B2 (en) 2002-04-19 2010-03-09 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7682318B2 (en) 2001-06-12 2010-03-23 Pelikan Technologies, Inc. Blood sampling apparatus and method
US7699791B2 (en) 2001-06-12 2010-04-20 Pelikan Technologies, Inc. Method and apparatus for improving success rate of blood yield from a fingerstick
US7713214B2 (en) 2002-04-19 2010-05-11 Pelikan Technologies, Inc. Method and apparatus for a multi-use body fluid sampling device with optical analyte sensing
US7717863B2 (en) 2002-04-19 2010-05-18 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7731729B2 (en) 2002-04-19 2010-06-08 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US20100194386A1 (en) * 2007-07-20 2010-08-05 Koninklijke Philips Electronics N.V. Magnetic sensor device
US7822454B1 (en) 2005-01-03 2010-10-26 Pelikan Technologies, Inc. Fluid sampling device with improved analyte detecting member configuration
US7833171B2 (en) 2002-04-19 2010-11-16 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US20100289483A1 (en) * 2007-07-20 2010-11-18 Koninklijke Philips Electronics N.V. Sensor cartridge
US20100297780A1 (en) * 2007-07-20 2010-11-25 Koninklijke Philips Electronics N.V. Methods and systems for detecting
US7841992B2 (en) 2001-06-12 2010-11-30 Pelikan Technologies, Inc. Tissue penetration device
US20100309472A1 (en) * 2007-11-05 2010-12-09 Koninklijke Philips Electronics N.V. Method for detecting redispersion of beads
US7850621B2 (en) 2003-06-06 2010-12-14 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US7862520B2 (en) 2002-04-19 2011-01-04 Pelikan Technologies, Inc. Body fluid sampling module with a continuous compression tissue interface surface
US7874994B2 (en) 2002-04-19 2011-01-25 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7892183B2 (en) 2002-04-19 2011-02-22 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
WO2011022173A1 (en) * 2009-08-21 2011-02-24 The Trustees Of The University Of Pennsylvania Bead based electrochemical biosensor
US7901362B2 (en) 2002-04-19 2011-03-08 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7909778B2 (en) 2002-04-19 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7909775B2 (en) 2001-06-12 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge
US7914465B2 (en) 2002-04-19 2011-03-29 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US20110073493A1 (en) * 2009-09-30 2011-03-31 Lifescan, Inc. Adhesive Composition for Use in an Immunosensor
US7959582B2 (en) 2002-04-19 2011-06-14 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US20110155585A1 (en) * 2009-12-30 2011-06-30 Lifescan, Inc. Systems, Devices, and Methods for Improving Accuracy of Biosensors Using Fill Time
US20110155584A1 (en) * 2009-12-30 2011-06-30 Lifescan, Inc. Systems, Devices, and Methods for Measuring Whole Blood Hematocrit Based on Initial Fill Velocity
US7976476B2 (en) 2002-04-19 2011-07-12 Pelikan Technologies, Inc. Device and method for variable speed lancet
US20120031773A1 (en) * 2010-08-05 2012-02-09 Abbott Point Of Care Immunoassay method and device with magnetically susceptible bead capture
WO2012042380A1 (en) 2010-09-30 2012-04-05 Cilag Gmbh International Systems and methods for improved stability of electrochemical sensors
US8197421B2 (en) 2002-04-19 2012-06-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8221334B2 (en) 2002-04-19 2012-07-17 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8267870B2 (en) 2002-04-19 2012-09-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling with hybrid actuation
US8282576B2 (en) 2003-09-29 2012-10-09 Sanofi-Aventis Deutschland Gmbh Method and apparatus for an improved sample capture device
US8333710B2 (en) 2002-04-19 2012-12-18 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8435190B2 (en) 2002-04-19 2013-05-07 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8439872B2 (en) 1998-03-30 2013-05-14 Sanofi-Aventis Deutschland Gmbh Apparatus and method for penetration with shaft having a sensor for sensing penetration depth
US8617370B2 (en) 2010-09-30 2013-12-31 Cilag Gmbh International Systems and methods of discriminating between a control sample and a test fluid using capacitance
US20140027310A1 (en) * 2012-07-27 2014-01-30 Ohmx Corporation Electric measurement of monolayers following pro-cleave detection of presence and activity of enzymes and other target analytes
US8652831B2 (en) 2004-12-30 2014-02-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte measurement test time
US20140048724A1 (en) * 2012-08-14 2014-02-20 Strategic Partnerships Alliance, LLC Antiseptic system using ultraviolet rays
US8668656B2 (en) 2003-12-31 2014-03-11 Sanofi-Aventis Deutschland Gmbh Method and apparatus for improving fluidic flow and sample capture
US8702624B2 (en) 2006-09-29 2014-04-22 Sanofi-Aventis Deutschland Gmbh Analyte measurement device with a single shot actuator
US8721671B2 (en) 2001-06-12 2014-05-13 Sanofi-Aventis Deutschland Gmbh Electric lancet actuator
US8828203B2 (en) 2004-05-20 2014-09-09 Sanofi-Aventis Deutschland Gmbh Printable hydrogels for biosensors
US8965476B2 (en) 2010-04-16 2015-02-24 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US9034639B2 (en) 2002-12-30 2015-05-19 Sanofi-Aventis Deutschland Gmbh Method and apparatus using optical techniques to measure analyte levels
US9072842B2 (en) 2002-04-19 2015-07-07 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US20150226735A1 (en) * 2012-09-19 2015-08-13 Universal Biosensors Pty Ltd Systems and methods for enzyme detection
US9122778B2 (en) 2009-05-27 2015-09-01 Biotempus Limited Methods of treating diseases
US9144401B2 (en) 2003-06-11 2015-09-29 Sanofi-Aventis Deutschland Gmbh Low pain penetrating member
RU2566605C2 (ru) * 2010-09-20 2015-10-27 Лайфскен, Инк. Устройство и способ усовершенствованных измерений посредством контрольно-измерительного устройства
US9226699B2 (en) 2002-04-19 2016-01-05 Sanofi-Aventis Deutschland Gmbh Body fluid sampling module with a continuous compression tissue interface surface
US9248267B2 (en) 2002-04-19 2016-02-02 Sanofi-Aventis Deustchland Gmbh Tissue penetration device
US9314194B2 (en) 2002-04-19 2016-04-19 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US9351680B2 (en) 2003-10-14 2016-05-31 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a variable user interface
RU2587501C2 (ru) * 2011-04-20 2016-06-20 Цилаг Гмбх Интернэшнл Электрохимические датчики с полем носителя
US9375169B2 (en) 2009-01-30 2016-06-28 Sanofi-Aventis Deutschland Gmbh Cam drive for managing disposable penetrating member actions with a single motor and motor and control system
US9386944B2 (en) 2008-04-11 2016-07-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte detecting device
US9404883B2 (en) 2012-07-27 2016-08-02 Ohmx Corporation Electronic measurements of monolayers following homogeneous reactions of their components
US9427532B2 (en) 2001-06-12 2016-08-30 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
CN105925696A (zh) * 2006-11-06 2016-09-07 科隆迪亚戈有限公司 使用结合元件用于分析的装置和方法
US9560993B2 (en) 2001-11-21 2017-02-07 Sanofi-Aventis Deutschland Gmbh Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means
US9795747B2 (en) 2010-06-02 2017-10-24 Sanofi-Aventis Deutschland Gmbh Methods and apparatus for lancet actuation
US9820684B2 (en) 2004-06-03 2017-11-21 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a fluid sampling device
US9839386B2 (en) 2002-04-19 2017-12-12 Sanofi-Aventis Deustschland Gmbh Body fluid sampling device with capacitive sensor
US9863931B2 (en) 2009-04-17 2018-01-09 Universal Biosensors Pty Ltd On-board control detection
WO2018067474A1 (en) 2016-10-03 2018-04-12 Abbott Laboratories Improved methods of assessing gfap status in patient samples
US9958440B2 (en) 2010-08-05 2018-05-01 Abbott Point Of Care Inc. Magnetic immunosensor and method of use
WO2018175942A1 (en) 2017-03-23 2018-09-27 Abbott Laboratories Methods for aiding in the diagnosis and determination of the extent of traumatic brain injury in a human subject using the early biomarker ubiquitin carboxy-terminal hydrolase l1
US10092669B2 (en) 2012-08-14 2018-10-09 Strategic Partnerships Alliance, LLC Sterilizing radiation system for use with door handle
WO2018191531A1 (en) 2017-04-15 2018-10-18 Abbott Laboratories Methods for aiding in the hyperacute diagnosis and determination of traumatic brain injury in a human subject using early biomarkers
WO2018200823A1 (en) 2017-04-28 2018-11-01 Abbott Laboratories Methods for aiding in the hyperacute diagnosis and determination of traumatic brain injury using early biomarkers on at least two samples from the same human subject
WO2018218169A1 (en) 2017-05-25 2018-11-29 Abbott Laboratories Methods for aiding in the determination of whether to perform imaging on a human subject who has sustained or may have sustained an injury to the head using early biomarkers
WO2018222783A1 (en) 2017-05-30 2018-12-06 Abbott Laboratories Methods for aiding in diagnosing and evaluating a mild traumatic brain injury in a human subject using cardiac troponin i and early biomarkers
WO2019010131A1 (en) 2017-07-03 2019-01-10 Abbott Laboratories IMPROVED METHODS FOR MEASURING CARBOXY TERMINATION HYDROLASE LEVELS OF UBIQUITIN L1 IN BLOOD
WO2019113525A2 (en) 2017-12-09 2019-06-13 Abbott Laboratories Methods for aiding in the diagnosis and evaluation of a subject who has sustained an orthopedic injury and that has or may have sustained an injury to the head, such as mild traumatic brain injury (tbi), using glial fibrillary acidic protein (gfap) and/or ubiquitin carboxy-terminal hydrolase l1 (uch-l1)
WO2019112860A1 (en) 2017-12-09 2019-06-13 Abbott Laboratories Methods for aiding in diagnosing and evaluating a traumatic brain injury in a human subject using a combination of gfap and uch-l1
WO2019133717A1 (en) 2017-12-29 2019-07-04 Abbott Laboratories Novel biomarkers and methods for diagnosing and evaluating traumatic brain injury
WO2020180695A1 (en) 2019-03-01 2020-09-10 Abbott Laboratories Methods for predicting major adverse cardiovascular events in subjects with coronary artery disease
WO2021211331A1 (en) 2020-04-13 2021-10-21 Abbott Point Of Care Inc. METHODS, COMPLEXES AND KITS FOR DETECTING OR DETERMINING AN AMOUNT OF A ß-CORONAVIRUS ANTIBODY IN A SAMPLE
WO2022031804A1 (en) 2020-08-04 2022-02-10 Abbott Laboratories Improved methods and kits for detecting sars-cov-2 protein in a sample
WO2022029494A1 (en) 2020-08-04 2022-02-10 Abbott Rapid Diagnostics International Unlimited Company Assays for detecting sars-cov-2
WO2022119841A1 (en) 2020-12-01 2022-06-09 Abbott Laboratories Use of one or more biomarkers to determine traumatic brain injury (tbi) in a subject having received a head computerized tomography scan that is negative for a tbi
US20220178920A1 (en) * 2020-03-11 2022-06-09 Newton Howard Cartridge-based automated rapid test analyzer
US20220187288A1 (en) * 2020-03-11 2022-06-16 Newton Howard Automated pathogen and antibody rapid test
WO2022147147A1 (en) 2020-12-30 2022-07-07 Abbott Laboratories Methods for determining sars-cov-2 antigen and anti-sars-cov-2 antibody in a sample
WO2022147178A1 (en) 2020-12-30 2022-07-07 Abbott Laboratories Improved methods, reagents and kits for detergent-based inactivation of betacoronavirus prior to and/or while assessing a biological sample for sars-cov-2 antigen or antibody
US20220214277A1 (en) * 2020-03-11 2022-07-07 Newton Howard Cartridge-based automated rapid test analyzer
US11402375B2 (en) 2010-08-05 2022-08-02 Abbott Point Of Care Inc. Magnetic immunosensor with trench configuration and method of use
WO2022245920A1 (en) 2021-05-18 2022-11-24 Abbott Laboratories Methods of evaluating brain injury in a pediatric subject
WO2022266034A1 (en) 2021-06-14 2022-12-22 Abbott Laboratories Methods of diagnosing or aiding in diagnosis of brain injury caused by acoustic energy, electromagnetic energy, an over pressurization wave, and/or blast wind
WO2023028186A1 (en) 2021-08-27 2023-03-02 Abbott Laboratories Methods for detecting immunoglobulin g, subclass 4 (igg4) in a biological sample
WO2023034777A1 (en) 2021-08-31 2023-03-09 Abbott Laboratories Methods and systems of diagnosing brain injury
WO2023056268A1 (en) 2021-09-30 2023-04-06 Abbott Laboratories Methods and systems of diagnosing brain injury
WO2023102384A1 (en) 2021-11-30 2023-06-08 Abbott Laboratories Use of one or more biomarkers to determine traumatic brain injury (tbi) in a subject having received a head computerized tomography scan that is negative for a tbi
WO2023114978A1 (en) 2021-12-17 2023-06-22 Abbott Laboratories Systems and methods for determining uch-l1, gfap, and other biomarkers in blood samples
WO2023129942A1 (en) 2021-12-28 2023-07-06 Abbott Laboratories Use of biomarkers to determine sub-acute traumatic brain injury (tbi) in a subject having received a head computerized tomography (ct) scan that is negative for a tbi or no head ct scan
WO2023154110A1 (en) 2022-02-11 2023-08-17 Abbott Point Of Care Inc. Apparatus and devices for processing fluid samples
WO2024006876A1 (en) 2022-06-29 2024-01-04 Abbott Laboratories Magnetic point-of-care systems and assays for determining gfap in biological samples
WO2024015493A1 (en) 2022-07-14 2024-01-18 Abbott Laboratories Methods and systems for malignancy prediction of indeterminate pulmonary nodules
WO2024044288A1 (en) 2022-08-26 2024-02-29 Abbott Laboratories Use of cardiac troponin and galectin-3 to differentiate myocardial infarction type i and type ii
WO2024059708A1 (en) 2022-09-15 2024-03-21 Abbott Laboratories Biomarkers and methods for differentiating between mild and supermild traumatic brain injury
WO2024102383A1 (en) 2022-11-10 2024-05-16 Abbott Laboratories Methods of identifying macrotroponin in biological samples
WO2024211475A1 (en) 2023-04-04 2024-10-10 Abbott Laboratories Use of biomarkers to determine whether a subject has sustained, may have sustained or is suspected of sustaining a subacute acquired brain injury (abi)
WO2024226971A1 (en) 2023-04-28 2024-10-31 Abbott Point Of Care Inc. Improved assays, cartridges, and kits for detection of biomarkers, including brain injury biomarkers
WO2024226899A1 (en) 2023-04-28 2024-10-31 Abbott Laboratories Diagnosis of late-stage hepatocellular carcinoma
WO2025145020A2 (en) 2023-12-28 2025-07-03 Abbott Laboratories Methods, systems, compounds, and kits for determining an analyte of interest in a test sample
WO2025193825A1 (en) 2024-03-13 2025-09-18 Abbott Laboratories Diagnosis and monitoring of liver disease
WO2025198859A1 (en) 2024-03-21 2025-09-25 Abbott Laboratories Synthesis of thyroid hormone derivatives and their role as calibrators for thyroid hormone immunoassays
WO2025230857A1 (en) 2024-05-01 2025-11-06 Abbott Laboratories Improved methods for determining cardiac myosin binding protein c in biological samples

Families Citing this family (38)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2505816C2 (ru) * 2008-03-17 2014-01-27 Конинклейке Филипс Электроникс Н.В. Картридж для анализов с помощью магнитных частиц
JP5224276B2 (ja) * 2008-05-02 2013-07-03 株式会社ティー・ティー・エム 体液成分の分析器具
US8389862B2 (en) 2008-10-07 2013-03-05 Mc10, Inc. Extremely stretchable electronics
US9123614B2 (en) 2008-10-07 2015-09-01 Mc10, Inc. Methods and applications of non-planar imaging arrays
EP2349440B1 (en) 2008-10-07 2019-08-21 Mc10, Inc. Catheter balloon having stretchable integrated circuitry and sensor array
US8097926B2 (en) 2008-10-07 2012-01-17 Mc10, Inc. Systems, methods, and devices having stretchable integrated circuitry for sensing and delivering therapy
EP2237027B1 (en) * 2009-04-03 2011-11-30 Nxp B.V. Sensor device and a method of manufacturing the same
WO2011041727A1 (en) 2009-10-01 2011-04-07 Mc10, Inc. Protective cases with integrated electronics
KR20130092571A (ko) 2010-08-02 2013-08-20 시락 게엠베하 인터내셔날 대조 용액에 대한 글루코스 결과의 온도 보정의 정확도 개선을 위한 시스템 및 방법
KR102000302B1 (ko) 2011-05-27 2019-07-15 엠씨10, 인크 전자, 광학, 및/또는 기계 장치 및 시스템, 그리고 이를 제조하기 위한 방법
WO2013022853A1 (en) 2011-08-05 2013-02-14 Mc10, Inc. Catheter balloon methods and apparatus employing sensing elements
US9226402B2 (en) 2012-06-11 2015-12-29 Mc10, Inc. Strain isolation structures for stretchable electronics
EP2866645A4 (en) 2012-07-05 2016-03-30 Mc10 Inc CATHETER DEVICE WITH FLOW MEASUREMENT
US9295842B2 (en) 2012-07-05 2016-03-29 Mc10, Inc. Catheter or guidewire device including flow sensing and use thereof
US9171794B2 (en) 2012-10-09 2015-10-27 Mc10, Inc. Embedding thin chips in polymer
KR20150072415A (ko) 2012-10-09 2015-06-29 엠씨10, 인크 의류에 집적되는 컨포멀 전자기기
US9706647B2 (en) 2013-05-14 2017-07-11 Mc10, Inc. Conformal electronics including nested serpentine interconnects
KR20160040670A (ko) 2013-08-05 2016-04-14 엠씨10, 인크 곡면부착형 전자기기를 포함하는 유연한 온도 센서
KR20160065948A (ko) 2013-10-07 2016-06-09 엠씨10, 인크 감지 및 분석용 등각 센서 시스템
JP6711750B2 (ja) 2013-11-22 2020-06-17 エムシー１０ インコーポレイテッドＭｃ１０，Ｉｎｃ． 心臓活動の検知および分析のためのコンフォーマルセンサシステム
CA2935372C (en) 2014-01-06 2023-08-08 Mc10, Inc. Encapsulated conformal electronic systems and devices, and methods of making and using the same
KR20160129007A (ko) 2014-03-04 2016-11-08 엠씨10, 인크 전자 디바이스를 위한 다부분 유연성 봉지 하우징
WO2015138712A1 (en) * 2014-03-12 2015-09-17 Mc10, Inc. Quantification of a change in assay
US9899330B2 (en) 2014-10-03 2018-02-20 Mc10, Inc. Flexible electronic circuits with embedded integrated circuit die
US10297572B2 (en) 2014-10-06 2019-05-21 Mc10, Inc. Discrete flexible interconnects for modules of integrated circuits
USD781270S1 (en) 2014-10-15 2017-03-14 Mc10, Inc. Electronic device having antenna
US10477354B2 (en) 2015-02-20 2019-11-12 Mc10, Inc. Automated detection and configuration of wearable devices based on on-body status, location, and/or orientation
WO2016140961A1 (en) 2015-03-02 2016-09-09 Mc10, Inc. Perspiration sensor
US10653332B2 (en) 2015-07-17 2020-05-19 Mc10, Inc. Conductive stiffener, method of making a conductive stiffener, and conductive adhesive and encapsulation layers
US10709384B2 (en) 2015-08-19 2020-07-14 Mc10, Inc. Wearable heat flux devices and methods of use
EP4079383A3 (en) 2015-10-01 2023-02-22 Medidata Solutions, Inc. Method and system for interacting with a virtual environment
US10532211B2 (en) 2015-10-05 2020-01-14 Mc10, Inc. Method and system for neuromodulation and stimulation
RU168959U1 (ru) * 2015-12-09 2017-02-28 Федеральное государственное бюджетное учреждение "Ростовский научно-исследовательский онкологический институт" Министерства здравоохранения Российской Федерации Устройство для проведения ранней диагностики несостоятельности анастомоза
EP3829187A1 (en) 2016-02-22 2021-06-02 Medidata Solutions, Inc. System, devices, and method for on-body data and power transmission
WO2017147053A1 (en) 2016-02-22 2017-08-31 Mc10, Inc. System, device, and method for coupled hub and sensor node on-body acquisition of sensor information
CN109310340A (zh) 2016-04-19 2019-02-05 Mc10股份有限公司 用于测量汗液的方法和系统
US10447347B2 (en) 2016-08-12 2019-10-15 Mc10, Inc. Wireless charger and high speed data off-loader
JP2019113460A (ja) * 2017-12-25 2019-07-11 大日本印刷株式会社 検査デバイス

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6245296B1 (en) * 1990-02-23 2001-06-12 The United States Of America As Represented By The Secretary Of The Navy Flow immunosensor apparatus
US6615856B2 (en) * 2000-08-04 2003-09-09 Biomicro Systems, Inc. Remote valving for microfluidic flow control
US20070250976A1 (en) * 2004-10-08 2007-11-01 Robert Beliveau Nose cover

Family Cites Families (166)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3552928A (en) 1967-07-19 1971-01-05 Miles Lab Whole blood separation means and test system using same
SE388694B (sv) 1975-01-27 1976-10-11 Kabi Ab Sett att pavisa ett antigen exv i prov av kroppvetskor, med utnyttjande av till porost berarmaterial bundna eller adsorberande antikroppar
JPS51114985A (en) 1975-04-01 1976-10-09 Kyoto Daiichi Kagaku:Kk Mothod to analyse urine, etc.
US4053381A (en) 1976-05-19 1977-10-11 Eastman Kodak Company Device for determining ionic activity of components of liquid drops
US4076596A (en) 1976-10-07 1978-02-28 Leeds & Northrup Company Apparatus for electrolytically determining a species in a fluid and method of use
AT360176B (de) 1977-07-01 1980-12-29 Roehm Gmbh Testkarte fuer den nachweis okkulten bluts im stuhl
JPS5912135B2 (ja) 1977-09-28 1984-03-21 松下電器産業株式会社 酵素電極
DE2913553C2 (de) 1979-04-04 1981-09-17 Boehringer Mannheim Gmbh, 6800 Mannheim Verfahren und Reagenz zur enzymatischen Bestimmung von Enzymsubstraten
US4376825A (en) 1979-05-07 1983-03-15 Syva Company Enzyme amplification compounds for assays for androgens
JPS5827352B2 (ja) 1979-08-31 1983-06-08 旭硝子株式会社 電極層付着イオン交換膜の製造法
US4298011A (en) 1979-09-07 1981-11-03 Mangurten Henry H Blood sample collector
US4301412A (en) 1979-10-29 1981-11-17 United States Surgical Corporation Liquid conductivity measuring system and sample cards therefor
US4301414A (en) 1979-10-29 1981-11-17 United States Surgical Corporation Disposable sample card and method of making same
US4323536A (en) 1980-02-06 1982-04-06 Eastman Kodak Company Multi-analyte test device
SE419903B (sv) 1980-03-05 1981-08-31 Enfors Sven Olof Enzymelektrod
US4404066A (en) 1980-08-25 1983-09-13 The Yellow Springs Instrument Company Method for quantitatively determining a particular substrate catalyzed by a multisubstrate enzyme
JPS57118152A (en) 1981-01-14 1982-07-22 Matsushita Electric Ind Co Ltd Enzyme electrode
US4426451A (en) * 1981-01-28 1984-01-17 Eastman Kodak Company Multi-zoned reaction vessel having pressure-actuatable control means between zones
US4446232A (en) 1981-10-13 1984-05-01 Liotta Lance A Enzyme immunoassay with two-zoned device having bound antigens
DE3278334D1 (en) 1981-10-23 1988-05-19 Genetics Int Inc Sensor for components of a liquid mixture
US4431004A (en) 1981-10-27 1984-02-14 Bessman Samuel P Implantable glucose sensor
US4468469A (en) 1981-11-04 1984-08-28 Miles Laboratories, Inc. Substituted phenylacetic acids and salts as TBP blocking agents in iodothyronine immunoassays
DE3228542A1 (de) 1982-07-30 1984-02-02 Siemens AG, 1000 Berlin und 8000 München Verfahren zur bestimmung der konzentration elektrochemisch umsetzbarer stoffe
US4426251A (en) 1982-09-29 1984-01-17 Storage Technology Corporation Portable gold recovery apparatus and method for using same
US4434236A (en) 1982-10-20 1984-02-28 E. I. Du Pont De Nemours & Co. Immunoassay wherein labeled antibody is displaced from immobilized analyte-analogue
US4552840A (en) 1982-12-02 1985-11-12 California And Hawaiian Sugar Company Enzyme electrode and method for dextran analysis
DE3247608A1 (de) 1982-12-23 1984-07-05 Boehringer Mannheim Gmbh, 6800 Mannheim Teststreifen
US5509410A (en) 1983-06-06 1996-04-23 Medisense, Inc. Strip electrode including screen printing of a single layer
CA1219040A (en) 1983-05-05 1987-03-10 Elliot V. Plotkin Measurement of enzyme-catalysed reactions
US4508821A (en) 1983-07-05 1985-04-02 Becton Dickinson And Company Detection of white cell associated bacteria with a fluorescent dye
US4533440A (en) 1983-08-04 1985-08-06 General Electric Company Method for continuous measurement of the sulfite/sulfate ratio
US4517291A (en) 1983-08-15 1985-05-14 E. I. Du Pont De Nemours And Company Biological detection process using polymer-coated electrodes
SE8305704D0 (sv) 1983-10-18 1983-10-18 Leo Ab Cuvette
US4637978A (en) 1983-10-28 1987-01-20 Eastman Kodak Company Assay for analysis of whole blood
US4508613A (en) 1983-12-19 1985-04-02 Gould Inc. Miniaturized potassium ion sensor
US4943533A (en) 1984-03-01 1990-07-24 The Regents Of The University Of California Hybrid cell lines that produce monoclonal antibodies to epidermal growth factor receptor
US4708929A (en) 1984-10-29 1987-11-24 Microgenics Corporation Methods for protein binding enzyme complementation assays
US5141868A (en) 1984-06-13 1992-08-25 Internationale Octrooi Maatschappij "Octropa" Bv Device for use in chemical test procedures
DE3568874D1 (en) 1984-06-13 1989-04-20 Ares Serono Inc Photometric instruments, their use in methods of optical analysis, and ancillary devices therefor
DE3506288A1 (de) 1984-09-06 1986-03-13 Johannes 7900 Ulm Reinmüller Vorrichtung zum einlegen in wunden und wundhoehlen
US4696748A (en) 1984-10-16 1987-09-29 Asahi Medical Co., Ltd. Plasma separator and a process for preparing the same
DE3587601T2 (de) 1984-10-18 1994-03-10 Chisso Corp Ferroelektrische chirale smektische Flüssigkristallzusammensetzung.
US4859583A (en) * 1985-02-25 1989-08-22 Amoco Corporation Chemiluminescent immunochemical technique for low molecular weight antigens
US4803170A (en) * 1985-05-09 1989-02-07 Ultra Diagnostics Corporation Competitive immunoassay method, device and test kit
US5185256A (en) 1985-06-21 1993-02-09 Matsushita Electric Industrial Co., Ltd. Method for making a biosensor
US4897173A (en) 1985-06-21 1990-01-30 Matsushita Electric Industrial Co., Ltd. Biosensor and method for making the same
DE3708031A1 (de) 1986-03-20 1987-11-12 Wolfgang Dr Med Wagner Messeinrichtung oder induktionseinrichtung mit messeinrichtung oder vorrichtung zur materialgewinnung fuer eine messvorrichtung fuer stoffwechselzustaende im blut mittels punktion unter anwendung von unterdruck innerhalb einer saugglocke bei verlagerung der messzone ausserhalb des spitzenbereiches des punktionsgeraetes
JPS636451A (ja) 1986-06-27 1988-01-12 Terumo Corp 酵素センサ
GB8618022D0 (en) 1986-07-23 1986-08-28 Unilever Plc Electrochemical measurements
US4935346A (en) 1986-08-13 1990-06-19 Lifescan, Inc. Minimum procedure system for the determination of analytes
US4790979A (en) 1986-08-29 1988-12-13 Technimed Corporation Test strip and fixture
WO1988004048A1 (en) 1986-11-28 1988-06-02 Unilever N.V. Electrochemical measurement devices and methods
EP0278647A3 (en) 1987-02-09 1989-09-20 AT&T Corp. Electronchemical processes involving enzymes
DE3705686C2 (de) 1987-02-23 1995-11-30 Boehringer Mannheim Gmbh Verfahren zur Bestimmung von Antikörpern
GB2201248B (en) 1987-02-24 1991-04-17 Ici Plc Enzyme electrode sensors
US4849340A (en) 1987-04-03 1989-07-18 Cardiovascular Diagnostics, Inc. Reaction system element and method for performing prothrombin time assay
ATE195022T1 (de) 1987-04-27 2000-08-15 Unilever Nv Spezifische bindungstestverfahren
US4943522A (en) 1987-06-01 1990-07-24 Quidel Lateral flow, non-bibulous membrane assay protocols
US4797256A (en) 1987-06-05 1989-01-10 Boehringer Mannheim Corporation Registration device for blood test strips
US4963815A (en) 1987-07-10 1990-10-16 Molecular Devices Corporation Photoresponsive electrode for determination of redox potential
US4883764A (en) 1987-07-20 1989-11-28 Kloepfer Mary A Blood test strip
US5128015A (en) 1988-03-15 1992-07-07 Tall Oak Ventures Method and apparatus for amperometric diagnostic analysis
DE68924026T3 (de) 1988-03-31 2008-01-10 Matsushita Electric Industrial Co., Ltd., Kadoma Biosensor und dessen herstellung.
FR2630546B1 (fr) 1988-04-20 1993-07-30 Centre Nat Rech Scient Electrode enzymatique et son procede de preparation
US4871258A (en) 1988-04-29 1989-10-03 Boehringer Mannheim Corporation Color test meter
US4994238A (en) 1988-06-09 1991-02-19 Daffern George M Constant volume chemical analysis test device
ES2100091T3 (es) 1988-06-09 1997-06-01 Boehringer Mannheim Corp Dispositivo de test de volumen definido.
CA1316572C (en) 1988-07-18 1993-04-20 Martin J. Patko Precalibrated, disposable, electrochemical sensors
GB8817421D0 (en) 1988-07-21 1988-08-24 Medisense Inc Bioelectrochemical electrodes
US5096809A (en) 1988-07-25 1992-03-17 Pacific Biotech, Inc. Whole blood assays using porous membrane support devices
US5312590A (en) 1989-04-24 1994-05-17 National University Of Singapore Amperometric sensor for single and multicomponent analysis
US5236567A (en) 1989-05-31 1993-08-17 Nakano Vinegar Co., Ltd. Enzyme sensor
US5272258A (en) 1989-06-29 1993-12-21 Rush-Presbyterian-St. Luke's Medical Center Monoclonal antibodies to C-reactive protein
DE3921528A1 (de) 1989-06-30 1991-01-10 Draegerwerk Ag Messzelle fuer den elektrochemischen gasnachweis
DE3921526A1 (de) 1989-06-30 1991-01-10 Draegerwerk Ag Diffusionsbarriere mit temperaturfuehler fuer einen elektrochemischen gassensor
DE3922495A1 (de) 1989-07-08 1991-01-17 Miles Inc Analyseverfahren fuer substanzen aus biologischen fluessigkeiten, insbesondere vollblut
AU640162B2 (en) 1989-08-28 1993-08-19 Lifescan, Inc. Blood separation and analyte detection techniques
US5306623A (en) 1989-08-28 1994-04-26 Lifescan, Inc. Visual blood glucose concentration test strip
CA2024548C (en) 1989-09-05 2002-05-28 David Issachar Analyte specific chemical sensor
DE69025134T2 (de) 1989-11-24 1996-08-14 Matsushita Electric Ind Co Ltd Verfahren zur Herstellung eines Biosensors
US5508171A (en) 1989-12-15 1996-04-16 Boehringer Mannheim Corporation Assay method with enzyme electrode system
DE4003194A1 (de) 1990-02-03 1991-08-08 Boehringer Mannheim Gmbh Verfahren und sensorelektrodensystem zur elektrochemischen bestimmung eines analyts oder einer oxidoreduktase sowie verwendung hierfuer geeigneter verbindungen
US5922615A (en) 1990-03-12 1999-07-13 Biosite Diagnostics Incorporated Assay devices comprising a porous capture membrane in fluid-withdrawing contact with a nonabsorbent capillary network
US5059908A (en) 1990-05-31 1991-10-22 Capital Controls Company, Inc. Amperimetric measurement with cell electrode deplating
US5320732A (en) 1990-07-20 1994-06-14 Matsushita Electric Industrial Co., Ltd. Biosensor and measuring apparatus using the same
FR2667943B1 (fr) 1990-10-11 1994-05-13 Jacques Toledano Dispositif et procede pour la determination qualitative et quantitative rapide d'un ligand dans un fluide.
ZA92804B (en) 1991-02-06 1992-12-30 Igen Inc Methods and apparatus for improved luminescence assays
DE69229629T2 (de) 1991-02-27 2002-05-16 Roche Diagnostics Corp., Indianapolis Stabilisierung eines enzym enthaltenden reagenz zur bestimmung eines analyten
US5192415A (en) 1991-03-04 1993-03-09 Matsushita Electric Industrial Co., Ltd. Biosensor utilizing enzyme and a method for producing the same
JP3118015B2 (ja) 1991-05-17 2000-12-18 アークレイ株式会社 バイオセンサーおよびそれを用いた分離定量方法
CA2074752A1 (en) 1991-07-29 1993-01-30 Tadakazu Yamauchi Process and device for specific binding assay
AU3104293A (en) 1992-01-14 1993-07-15 Commonwealth Scientific And Industrial Research Organisation Viscometer
EP0560336B1 (en) 1992-03-12 1998-05-06 Matsushita Electric Industrial Co., Ltd. A biosensor including a catalyst made from phosphate
GR1002549B (el) 1992-05-12 1997-01-28 Lifescan Inc. Λωρις εξετασεως με μεταφορικο μεσο δια μεταφορα ρευστου.
GB9212416D0 (en) 1992-06-11 1992-07-22 Medical Res Council Reversible binding substances
WO1994003496A1 (en) 1992-07-30 1994-02-17 Commonwealth Scientific And Industrial Research Organisation Biomaterials and biosensors containing immobilized modified antibodies
JP2541081B2 (ja) 1992-08-28 1996-10-09 日本電気株式会社 バイオセンサ及びバイオセンサの製造・使用方法
FR2695481B1 (fr) 1992-09-07 1994-12-02 Cylergie Gie Dispositif de mesure ampérométrique comportant un capteur électrochimique.
JPH06214365A (ja) 1992-12-14 1994-08-05 Eastman Kodak Co 漂白促進剤、漂白組成物及び写真要素
US5372932A (en) 1992-12-22 1994-12-13 Eastman Kodak Company Analytical element and method for the determination of a specific binding ligand using a 4-hydroxy or 4-alkoxyarylacetamide as stabilizer
JP3217066B2 (ja) 1993-01-28 2001-10-09 ロシュ ダイアグノスティックス コーポレーション アナライトの嫌気的定量に有用な組成物
FR2701117B1 (fr) 1993-02-04 1995-03-10 Asulab Sa Système de mesures électrochimiques à capteur multizones, et son application au dosage du glucose.
US5268890A (en) 1993-02-09 1993-12-07 Delco Electronics Corporation Self-cleaning optical disc system
NL9300642A (nl) 1993-04-15 1994-11-01 Tno Werkwijze voor de vervaardiging van keramische holle vezels, in het bijzonder holle vezelmembranen voor microfiltratie, ultrafiltratie en gasscheiding.
US5385846A (en) 1993-06-03 1995-01-31 Boehringer Mannheim Corporation Biosensor and method for hematocrit determination
US5413690A (en) 1993-07-23 1995-05-09 Boehringer Mannheim Corporation Potentiometric biosensor and the method of its use
EP0640836A3 (en) 1993-08-24 1995-12-20 Wako Pure Chem Ind Ltd Immunoassay.
US5427912A (en) 1993-08-27 1995-06-27 Boehringer Mannheim Corporation Electrochemical enzymatic complementation immunoassay
US5494831A (en) 1993-08-30 1996-02-27 Hughes Aircraft Company Electrochemical immunosensor system and methods
GB9325189D0 (en) 1993-12-08 1994-02-09 Unilever Plc Methods and apparatus for electrochemical measurements
GB9402591D0 (en) 1994-02-10 1994-04-06 Univ Cranfield Hexacyanoferrate (III) modified carbon electrodes
US5437999A (en) 1994-02-22 1995-08-01 Boehringer Mannheim Corporation Electrochemical sensor
AUPM506894A0 (en) 1994-04-14 1994-05-05 Memtec Limited Novel electrochemical cells
US5518590A (en) 1994-06-21 1996-05-21 Pennzoil Products Company Electrochemical sensors for motor oils and other lubricants
ZA956882B (en) 1994-08-29 1996-03-25 Cabot Corp Universal masterbatch
JPH08136496A (ja) 1994-11-02 1996-05-31 Taizo Uda バイオセンサー
WO1996014582A1 (fr) 1994-11-07 1996-05-17 Laboratoires Merck-Clevenot Appareil automatique de dosage immunologique
AUPN239395A0 (en) 1995-04-12 1995-05-11 Memtec Limited Method of defining an electrode area
US5620579A (en) 1995-05-05 1997-04-15 Bayer Corporation Apparatus for reduction of bias in amperometric sensors
US5567302A (en) 1995-06-07 1996-10-22 Molecular Devices Corporation Electrochemical system for rapid detection of biochemical agents that catalyze a redox potential change
AUPN363995A0 (en) 1995-06-19 1995-07-13 Memtec Limited Electrochemical cell
US5665215A (en) 1995-09-25 1997-09-09 Bayer Corporation Method and apparatus for making predetermined events with a biosensor
US5628890A (en) 1995-09-27 1997-05-13 Medisense, Inc. Electrochemical sensor
US6638415B1 (en) 1995-11-16 2003-10-28 Lifescan, Inc. Antioxidant sensor
AUPN661995A0 (en) 1995-11-16 1995-12-07 Memtec America Corporation Electrochemical cell 2
AUPP238898A0 (en) 1998-03-12 1998-04-09 Usf Filtration And Separations Group Inc. Heated electrochemical cell
IL116921A (en) 1996-01-26 2000-11-21 Yissum Res Dev Co Electrochemical system for determination of an analyte in a liquid medium
CA2198955A1 (en) 1996-03-22 1997-09-22 Ferdon H. Crawford Pipette for collecting and dispensing material samples
US6001307A (en) 1996-04-26 1999-12-14 Kyoto Daiichi Kagaku Co., Ltd. Device for analyzing a sample
US5951492A (en) 1996-05-17 1999-09-14 Mercury Diagnostics, Inc. Methods and apparatus for sampling and analyzing body fluid
US5776324A (en) 1996-05-17 1998-07-07 Encelle, Inc. Electrochemical biosensors
AUPO229696A0 (en) 1996-09-13 1996-10-10 Memtec America Corporation Analytic cell
GB9622524D0 (en) * 1996-10-29 1997-01-08 London Biotechnology Ltd Enzyme labels for assays
FR2755013B1 (fr) 1996-10-29 1998-11-27 Rhone Poulenc Rorer Sa Nouvelle application therapeutique des antagonistes de la substance p
US6632349B1 (en) 1996-11-15 2003-10-14 Lifescan, Inc. Hemoglobin sensor
ES2297337T3 (es) 1997-01-31 2008-05-01 Ric Investments, Inc. Sistema de absorcion por oscilacion de presion que comprende un bote de camaras multiples.
JPH10221341A (ja) 1997-02-03 1998-08-21 Mitsui Chem Inc 体液中の遊離リガンドの測定方法
KR20000070821A (ko) 1997-02-06 2000-11-25 프란시스 제이 메이어 특이적 결합의 전기화학적 검출
US5932711A (en) 1997-03-05 1999-08-03 Mosaic Technologies, Inc. Nucleic acid-containing polymerizable complex
AUPO581397A0 (en) 1997-03-21 1997-04-17 Memtec America Corporation Sensor connection means
AUPO585797A0 (en) * 1997-03-25 1997-04-24 Memtec America Corporation Improved electrochemical cell
US6054039A (en) 1997-08-18 2000-04-25 Shieh; Paul Determination of glycoprotein and glycosylated hemoglobin in blood
US6193865B1 (en) 1997-09-11 2001-02-27 Usf Filtration And Separations Group, Inc. Analytic cell
US5842787A (en) 1997-10-09 1998-12-01 Caliper Technologies Corporation Microfluidic systems incorporating varied channel dimensions
DE19822123C2 (de) * 1997-11-21 2003-02-06 Meinhard Knoll Verfahren und Vorrichtung zum Nachweis von Analyten
US5997817A (en) 1997-12-05 1999-12-07 Roche Diagnostics Corporation Electrochemical biosensor test strip
US6103033A (en) 1998-03-04 2000-08-15 Therasense, Inc. Process for producing an electrochemical biosensor
AUPP250398A0 (en) 1998-03-20 1998-04-23 Usf Filtration And Separations Group Inc. Sensor with improved shelf life
JP3874321B2 (ja) 1998-06-11 2007-01-31 松下電器産業株式会社 バイオセンサ
ID27647A (id) 1998-07-02 2001-04-19 Molecular Circuitry Inc Perangkat dan wadah penguji immunoassay
JP2002536660A (ja) * 1999-02-11 2002-10-29 ユニバーシティ・オブ・サザン・カリフォルニア 酵素結合の免疫磁気性電気化学的バイオセンサー
WO2001006244A2 (en) 1999-07-16 2001-01-25 Board Of Regents, The University Of Texas System General signaling protocols for chemical receptors in immobilized matrices
US6495823B1 (en) 1999-07-21 2002-12-17 The Charles Stark Draper Laboratory, Inc. Micromachined field asymmetric ion mobility filter and detection system
JP2001059845A (ja) 1999-08-24 2001-03-06 Fuji Photo Film Co Ltd 乾式分析方法及び乾式分析要素
JP2001153838A (ja) * 1999-11-29 2001-06-08 Matsushita Electric Ind Co Ltd アレルゲン測定電極およびアレルゲン測定装置
US6649403B1 (en) 2000-01-31 2003-11-18 Board Of Regents, The University Of Texas Systems Method of preparing a sensor array
US6571651B1 (en) 2000-03-27 2003-06-03 Lifescan, Inc. Method of preventing short sampling of a capillary or wicking fill device
RU2278612C2 (ru) 2000-07-14 2006-06-27 Лайфскен, Инк. Иммуносенсор
ES2277933T3 (es) * 2000-07-14 2007-08-01 Lifescan, Inc. Procedimiento electroquimico para medir la velocidad de reacciones quimicas.
CA2733852A1 (en) * 2000-07-14 2002-01-24 Lifescan, Inc. Electrochemical method for measuring chemical reaction rates
US6444115B1 (en) 2000-07-14 2002-09-03 Lifescan, Inc. Electrochemical method for measuring chemical reaction rates
US7018518B2 (en) * 2002-02-04 2006-03-28 Yissum Research Development Company Of The Hebrew University Of Jerusalem Biosensor carrying redox enzymes
US20030180814A1 (en) 2002-03-21 2003-09-25 Alastair Hodges Direct immunosensor assay
CA2530211C (en) * 2003-07-01 2011-10-04 Eric R. Diebold Electrochemical affinity biosensor system and methods
US7723099B2 (en) * 2003-09-10 2010-05-25 Abbott Point Of Care Inc. Immunoassay device with immuno-reference electrode
CN107104152B (zh) 2017-05-23 2020-04-21 京东方科技集团股份有限公司 薄膜晶体管及其制造方法、显示基板、显示面板

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6245296B1 (en) * 1990-02-23 2001-06-12 The United States Of America As Represented By The Secretary Of The Navy Flow immunosensor apparatus
US6615856B2 (en) * 2000-08-04 2003-09-09 Biomicro Systems, Inc. Remote valving for microfluidic flow control
US20070250976A1 (en) * 2004-10-08 2007-11-01 Robert Beliveau Nose cover

Cited By (242)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7666149B2 (en) 1997-12-04 2010-02-23 Peliken Technologies, Inc. Cassette of lancet cartridges for sampling blood
US8439872B2 (en) 1998-03-30 2013-05-14 Sanofi-Aventis Deutschland Gmbh Apparatus and method for penetration with shaft having a sensor for sensing penetration depth
US20090041760A1 (en) * 2000-08-18 2009-02-12 Martin Leonard Ashdown Retroviral immunotherapy
US7582063B2 (en) 2000-11-21 2009-09-01 Pelikan Technologies, Inc. Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means
US8206319B2 (en) 2001-06-12 2012-06-26 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8622930B2 (en) 2001-06-12 2014-01-07 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US7316700B2 (en) 2001-06-12 2008-01-08 Pelikan Technologies, Inc. Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties
US9694144B2 (en) 2001-06-12 2017-07-04 Sanofi-Aventis Deutschland Gmbh Sampling module device and method
US9427532B2 (en) 2001-06-12 2016-08-30 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8382683B2 (en) 2001-06-12 2013-02-26 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8641643B2 (en) 2001-06-12 2014-02-04 Sanofi-Aventis Deutschland Gmbh Sampling module device and method
US8360991B2 (en) 2001-06-12 2013-01-29 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8343075B2 (en) 2001-06-12 2013-01-01 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US7909775B2 (en) 2001-06-12 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge
US8282577B2 (en) 2001-06-12 2012-10-09 Sanofi-Aventis Deutschland Gmbh Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge
US8679033B2 (en) 2001-06-12 2014-03-25 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8216154B2 (en) 2001-06-12 2012-07-10 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US7537571B2 (en) 2001-06-12 2009-05-26 Pelikan Technologies, Inc. Integrated blood sampling analysis system with multi-use sampling module
US8211037B2 (en) 2001-06-12 2012-07-03 Pelikan Technologies, Inc. Tissue penetration device
US7841992B2 (en) 2001-06-12 2010-11-30 Pelikan Technologies, Inc. Tissue penetration device
US8206317B2 (en) 2001-06-12 2012-06-26 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8721671B2 (en) 2001-06-12 2014-05-13 Sanofi-Aventis Deutschland Gmbh Electric lancet actuator
US8162853B2 (en) 2001-06-12 2012-04-24 Pelikan Technologies, Inc. Tissue penetration device
US9802007B2 (en) 2001-06-12 2017-10-31 Sanofi-Aventis Deutschland Gmbh Methods and apparatus for lancet actuation
US8845550B2 (en) 2001-06-12 2014-09-30 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8123700B2 (en) 2001-06-12 2012-02-28 Pelikan Technologies, Inc. Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge
US8016774B2 (en) 2001-06-12 2011-09-13 Pelikan Technologies, Inc. Tissue penetration device
US7988645B2 (en) 2001-06-12 2011-08-02 Pelikan Technologies, Inc. Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties
US7682318B2 (en) 2001-06-12 2010-03-23 Pelikan Technologies, Inc. Blood sampling apparatus and method
US7699791B2 (en) 2001-06-12 2010-04-20 Pelikan Technologies, Inc. Method and apparatus for improving success rate of blood yield from a fingerstick
US7981055B2 (en) 2001-06-12 2011-07-19 Pelikan Technologies, Inc. Tissue penetration device
US7850622B2 (en) 2001-06-12 2010-12-14 Pelikan Technologies, Inc. Tissue penetration device
US7344894B2 (en) 2001-10-16 2008-03-18 Agilent Technologies, Inc. Thermal regulation of fluidic samples within a diagnostic cartridge
US9560993B2 (en) 2001-11-21 2017-02-07 Sanofi-Aventis Deutschland Gmbh Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means
US20040137141A1 (en) * 2001-11-28 2004-07-15 Dick Kenneth W. Solution drying system
US20050180971A1 (en) * 2002-02-14 2005-08-18 Ashdown Martin L. Cancer therapy
US9186468B2 (en) 2002-04-19 2015-11-17 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7674232B2 (en) 2002-04-19 2010-03-09 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9498160B2 (en) 2002-04-19 2016-11-22 Sanofi-Aventis Deutschland Gmbh Method for penetrating tissue
US7833171B2 (en) 2002-04-19 2010-11-16 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9724021B2 (en) 2002-04-19 2017-08-08 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8337419B2 (en) 2002-04-19 2012-12-25 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8579831B2 (en) 2002-04-19 2013-11-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7862520B2 (en) 2002-04-19 2011-01-04 Pelikan Technologies, Inc. Body fluid sampling module with a continuous compression tissue interface surface
US7874994B2 (en) 2002-04-19 2011-01-25 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7892183B2 (en) 2002-04-19 2011-02-22 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US7344507B2 (en) 2002-04-19 2008-03-18 Pelikan Technologies, Inc. Method and apparatus for lancet actuation
US7901362B2 (en) 2002-04-19 2011-03-08 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7909778B2 (en) 2002-04-19 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7297151B2 (en) 2002-04-19 2007-11-20 Elikan Technologies, Inc. Method and apparatus for body fluid sampling with improved sensing
US7959582B2 (en) 2002-04-19 2011-06-14 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7909777B2 (en) 2002-04-19 2011-03-22 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US7914465B2 (en) 2002-04-19 2011-03-29 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9314194B2 (en) 2002-04-19 2016-04-19 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8435190B2 (en) 2002-04-19 2013-05-07 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7938787B2 (en) 2002-04-19 2011-05-10 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9248267B2 (en) 2002-04-19 2016-02-02 Sanofi-Aventis Deustchland Gmbh Tissue penetration device
US9226699B2 (en) 2002-04-19 2016-01-05 Sanofi-Aventis Deutschland Gmbh Body fluid sampling module with a continuous compression tissue interface surface
US7909774B2 (en) 2002-04-19 2011-03-22 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7731729B2 (en) 2002-04-19 2010-06-08 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7717863B2 (en) 2002-04-19 2010-05-18 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9089678B2 (en) 2002-04-19 2015-07-28 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US9089294B2 (en) 2002-04-19 2015-07-28 Sanofi-Aventis Deutschland Gmbh Analyte measurement device with a single shot actuator
US7976476B2 (en) 2002-04-19 2011-07-12 Pelikan Technologies, Inc. Device and method for variable speed lancet
US7713214B2 (en) 2002-04-19 2010-05-11 Pelikan Technologies, Inc. Method and apparatus for a multi-use body fluid sampling device with optical analyte sensing
US7981056B2 (en) 2002-04-19 2011-07-19 Pelikan Technologies, Inc. Methods and apparatus for lancet actuation
US7988644B2 (en) 2002-04-19 2011-08-02 Pelikan Technologies, Inc. Method and apparatus for a multi-use body fluid sampling device with sterility barrier release
US8337420B2 (en) 2002-04-19 2012-12-25 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US9072842B2 (en) 2002-04-19 2015-07-07 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8007446B2 (en) 2002-04-19 2011-08-30 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9795334B2 (en) 2002-04-19 2017-10-24 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8333710B2 (en) 2002-04-19 2012-12-18 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US8062231B2 (en) 2002-04-19 2011-11-22 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8079960B2 (en) 2002-04-19 2011-12-20 Pelikan Technologies, Inc. Methods and apparatus for lancet actuation
US8430828B2 (en) 2002-04-19 2013-04-30 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a multi-use body fluid sampling device with sterility barrier release
US8905945B2 (en) 2002-04-19 2014-12-09 Dominique M. Freeman Method and apparatus for penetrating tissue
US8414503B2 (en) 2002-04-19 2013-04-09 Sanofi-Aventis Deutschland Gmbh Methods and apparatus for lancet actuation
US7648468B2 (en) 2002-04-19 2010-01-19 Pelikon Technologies, Inc. Method and apparatus for penetrating tissue
US8403864B2 (en) 2002-04-19 2013-03-26 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8388551B2 (en) 2002-04-19 2013-03-05 Sanofi-Aventis Deutschland Gmbh Method and apparatus for multi-use body fluid sampling device with sterility barrier release
US8382682B2 (en) 2002-04-19 2013-02-26 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US8197423B2 (en) 2002-04-19 2012-06-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8197421B2 (en) 2002-04-19 2012-06-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8202231B2 (en) 2002-04-19 2012-06-19 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7582099B2 (en) 2002-04-19 2009-09-01 Pelikan Technologies, Inc Method and apparatus for penetrating tissue
US7563232B2 (en) 2002-04-19 2009-07-21 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7547287B2 (en) 2002-04-19 2009-06-16 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8690796B2 (en) 2002-04-19 2014-04-08 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7524293B2 (en) 2002-04-19 2009-04-28 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8221334B2 (en) 2002-04-19 2012-07-17 Sanofi-Aventis Deutschland Gmbh Method and apparatus for penetrating tissue
US7491178B2 (en) 2002-04-19 2009-02-17 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US7481776B2 (en) 2002-04-19 2009-01-27 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US8267870B2 (en) 2002-04-19 2012-09-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling with hybrid actuation
US7374544B2 (en) 2002-04-19 2008-05-20 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9839386B2 (en) 2002-04-19 2017-12-12 Sanofi-Aventis Deustschland Gmbh Body fluid sampling device with capacitive sensor
US7410468B2 (en) 2002-04-19 2008-08-12 Pelikan Technologies, Inc. Method and apparatus for penetrating tissue
US9034639B2 (en) 2002-12-30 2015-05-19 Sanofi-Aventis Deutschland Gmbh Method and apparatus using optical techniques to measure analyte levels
US8251921B2 (en) 2003-06-06 2012-08-28 Sanofi-Aventis Deutschland Gmbh Method and apparatus for body fluid sampling and analyte sensing
US7850621B2 (en) 2003-06-06 2010-12-14 Pelikan Technologies, Inc. Method and apparatus for body fluid sampling and analyte sensing
US10034628B2 (en) 2003-06-11 2018-07-31 Sanofi-Aventis Deutschland Gmbh Low pain penetrating member
US9144401B2 (en) 2003-06-11 2015-09-29 Sanofi-Aventis Deutschland Gmbh Low pain penetrating member
US7604592B2 (en) 2003-06-13 2009-10-20 Pelikan Technologies, Inc. Method and apparatus for a point of care device
US8282576B2 (en) 2003-09-29 2012-10-09 Sanofi-Aventis Deutschland Gmbh Method and apparatus for an improved sample capture device
US8945910B2 (en) 2003-09-29 2015-02-03 Sanofi-Aventis Deutschland Gmbh Method and apparatus for an improved sample capture device
US9351680B2 (en) 2003-10-14 2016-05-31 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a variable user interface
US8524651B2 (en) 2003-10-24 2013-09-03 Immunaid Pty Ltd. Method of therapy
US20070202119A1 (en) * 2003-10-24 2007-08-30 Ashdown Martin L Method Of Therapy
US8296918B2 (en) 2003-12-31 2012-10-30 Sanofi-Aventis Deutschland Gmbh Method of manufacturing a fluid sampling device with improved analyte detecting member configuration
US9561000B2 (en) 2003-12-31 2017-02-07 Sanofi-Aventis Deutschland Gmbh Method and apparatus for improving fluidic flow and sample capture
US8668656B2 (en) 2003-12-31 2014-03-11 Sanofi-Aventis Deutschland Gmbh Method and apparatus for improving fluidic flow and sample capture
US8828203B2 (en) 2004-05-20 2014-09-09 Sanofi-Aventis Deutschland Gmbh Printable hydrogels for biosensors
US9261476B2 (en) 2004-05-20 2016-02-16 Sanofi Sa Printable hydrogel for biosensors
US9820684B2 (en) 2004-06-03 2017-11-21 Sanofi-Aventis Deutschland Gmbh Method and apparatus for a fluid sampling device
US20080248022A1 (en) * 2004-09-08 2008-10-09 Immunaid Pty Ltd Therapeutic Strategy for Treating Autoimmune and Degenerative Diseases
US8652831B2 (en) 2004-12-30 2014-02-18 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte measurement test time
US7822454B1 (en) 2005-01-03 2010-10-26 Pelikan Technologies, Inc. Fluid sampling device with improved analyte detecting member configuration
US8192599B2 (en) 2005-05-25 2012-06-05 Universal Biosensors Pty Ltd Method and apparatus for electrochemical analysis
US20070205103A1 (en) * 2005-05-25 2007-09-06 Lifescan, Inc. Method and apparatus for electrochemical analysis
US20060266644A1 (en) * 2005-05-25 2006-11-30 Lifescan, Inc. Method and apparatus for electrochemical analysis
US8323464B2 (en) 2005-05-25 2012-12-04 Universal Biosensors Pty Ltd Method and apparatus for electrochemical analysis
US20090305431A1 (en) * 2006-02-21 2009-12-10 Universal Biosensors Pty Ltd. Fluid transfer mechanism
US8182765B2 (en) 2006-02-21 2012-05-22 Universal Biosensors Pty Ltd Fluid transfer mechanism
US8702624B2 (en) 2006-09-29 2014-04-22 Sanofi-Aventis Deutschland Gmbh Analyte measurement device with a single shot actuator
CN109055495A (zh) * 2006-11-06 2018-12-21 美艾利尔技术公司 使用结合元件用于分析的装置和方法
CN105925696A (zh) * 2006-11-06 2016-09-07 科隆迪亚戈有限公司 使用结合元件用于分析的装置和方法
US20100297780A1 (en) * 2007-07-20 2010-11-25 Koninklijke Philips Electronics N.V. Methods and systems for detecting
US20100289483A1 (en) * 2007-07-20 2010-11-18 Koninklijke Philips Electronics N.V. Sensor cartridge
US9778254B2 (en) 2007-07-20 2017-10-03 Koninklijke Philips N.V. Methods and systems for detecting
US20100194386A1 (en) * 2007-07-20 2010-08-05 Koninklijke Philips Electronics N.V. Magnetic sensor device
WO2009018348A1 (en) * 2007-07-30 2009-02-05 Cornell Research Foundation, Inc. Microchannel detection device and use thereof
US20100227323A1 (en) * 2007-07-30 2010-09-09 Cornell Research Foundation, Inc. Microchannel detection device and use thereof
US8339608B2 (en) 2007-11-05 2012-12-25 Koninklijke Philips Electronics N.V. Method for detecting redispersion of beads
US20100309472A1 (en) * 2007-11-05 2010-12-09 Koninklijke Philips Electronics N.V. Method for detecting redispersion of beads
US9386944B2 (en) 2008-04-11 2016-07-12 Sanofi-Aventis Deutschland Gmbh Method and apparatus for analyte detecting device
CN102105790B (zh) * 2008-07-11 2017-09-01 环球生物医疗感测器私人有限公司 增强之免疫测定传感器
CN102105790A (zh) * 2008-07-11 2011-06-22 环球生物医疗感测器私人有限公司 增强之免疫测定传感器
EP2318837A4 (en) * 2008-07-11 2011-09-21 Universal Biosensors Pty Ltd IMPROVED IMMUNOASSAY SENSOR
TWI485403B (zh) * 2008-07-11 2015-05-21 Universal Biosensors Pty Ltd 增強之免疫測定感測器
US8951749B2 (en) 2008-07-11 2015-02-10 Universal Biosensors Pty Ltd Enhanced immunoassay sensor
WO2010004436A3 (en) * 2008-07-11 2010-02-25 University Biosensors Pty Ltd. Enhanced immunoassay sensor
AU2009269702B2 (en) * 2008-07-11 2016-07-21 Universal Biosensors Pty Ltd Enhanced immunoassay sensor
KR101644144B1 (ko) * 2008-07-11 2016-07-29 유니버셜 바이오센서스 피티와이 엘티디. 향상된 면역분석 센서
US20110111425A1 (en) * 2008-07-11 2011-05-12 Universal Birosensors Pty Ltd. Enhanced immunoassay sensor
KR20110050446A (ko) * 2008-07-11 2011-05-13 유니버셜 바이오센서스 피티와이 엘티디. 향상된 면역분석 센서
US9375169B2 (en) 2009-01-30 2016-06-28 Sanofi-Aventis Deutschland Gmbh Cam drive for managing disposable penetrating member actions with a single motor and motor and control system
US9863931B2 (en) 2009-04-17 2018-01-09 Universal Biosensors Pty Ltd On-board control detection
US9239904B2 (en) 2009-05-27 2016-01-19 Biotempus Limited Computer systems for treating diseases
EP2982978A1 (en) 2009-05-27 2016-02-10 Immunaid Pty Ltd Methods of treating diseases
US9268908B2 (en) 2009-05-27 2016-02-23 Biotempus Limited Computer systems for treating diseases
US9122778B2 (en) 2009-05-27 2015-09-01 Biotempus Limited Methods of treating diseases
US10714208B2 (en) 2009-05-27 2020-07-14 Biotempus Pty Ltd Computer systems for treating diseases
WO2011022173A1 (en) * 2009-08-21 2011-02-24 The Trustees Of The University Of Pennsylvania Bead based electrochemical biosensor
US8221994B2 (en) 2009-09-30 2012-07-17 Cilag Gmbh International Adhesive composition for use in an immunosensor
EP2472261A1 (en) 2009-09-30 2012-07-04 Cilag GmbH International Adhesive composition for use in an immunosensor
EP2306196A1 (en) * 2009-09-30 2011-04-06 Cilag GmbH International Adhesive compositon for use in an immunosensor
US20110073493A1 (en) * 2009-09-30 2011-03-31 Lifescan, Inc. Adhesive Composition for Use in an Immunosensor
KR101233740B1 (ko) 2009-09-30 2013-02-18 시락 게엠베하 인터내셔날 면역센서에 사용하기 위한 접착 조성물
US8758592B2 (en) 2009-09-30 2014-06-24 Cilag Gmbh International Adhesive composition for use in an immunosensor
JP2017203783A (ja) * 2009-12-30 2017-11-16 ライフスキャン・インコーポレイテッドＬｉｆｅｓｃａｎ，Ｉｎｃ． 充填時間を使用してバイオセンサーの精度を改善するためのシステム、装置及び方法
US8877034B2 (en) 2009-12-30 2014-11-04 Lifescan, Inc. Systems, devices, and methods for measuring whole blood hematocrit based on initial fill velocity
US9404888B2 (en) 2009-12-30 2016-08-02 Lifescan, Inc. Systems, devices and methods for improving accuracy of biosensors using fill time
EP3349009A1 (en) 2009-12-30 2018-07-18 Lifescan, Inc. Systems, devices and methods for improving accuracy of biosensors using fill time
EP3349008A1 (en) 2009-12-30 2018-07-18 Lifescan, Inc. Systems, devices and methods for improving accuracy of biosensors using fill time
US9927388B2 (en) 2009-12-30 2018-03-27 Lifescan, Inc. Systems, devices, and methods for measuring whole blood hematocrit based on initial fill velocity
US8623198B2 (en) 2009-12-30 2014-01-07 Lifescan, Inc. Systems, devices, and methods for improving accuracy of biosensors using fill time
US20110155585A1 (en) * 2009-12-30 2011-06-30 Lifescan, Inc. Systems, Devices, and Methods for Improving Accuracy of Biosensors Using Fill Time
US8101065B2 (en) 2009-12-30 2012-01-24 Lifescan, Inc. Systems, devices, and methods for improving accuracy of biosensors using fill time
US20110155589A1 (en) * 2009-12-30 2011-06-30 Lifescan, Inc. Systems, Devices, and Methods for Improving Accuracy of Biosensors Using Fill Time
EP2341342A3 (en) * 2009-12-30 2015-04-01 Lifescan, Inc. Systems, devices, and methods for measuring whole blood hematocrit based on initial fill velocity
EP2360477A1 (en) 2009-12-30 2011-08-24 Lifescan, Inc. Systems, devices and methods for improving accuracy of biosensors using fill time
EP3182127A1 (en) 2009-12-30 2017-06-21 Lifescan, Inc. Systems, devices and methods for improving accuracy of biosensors using fill time
US20110155584A1 (en) * 2009-12-30 2011-06-30 Lifescan, Inc. Systems, Devices, and Methods for Measuring Whole Blood Hematocrit Based on Initial Fill Velocity
US8965476B2 (en) 2010-04-16 2015-02-24 Sanofi-Aventis Deutschland Gmbh Tissue penetration device
US9795747B2 (en) 2010-06-02 2017-10-24 Sanofi-Aventis Deutschland Gmbh Methods and apparatus for lancet actuation
US10126296B2 (en) * 2010-08-05 2018-11-13 Abbott Point Of Care Inc. Immunoassay method and device with magnetically susceptible bead capture
US20120031773A1 (en) * 2010-08-05 2012-02-09 Abbott Point Of Care Immunoassay method and device with magnetically susceptible bead capture
US11402375B2 (en) 2010-08-05 2022-08-02 Abbott Point Of Care Inc. Magnetic immunosensor with trench configuration and method of use
US9958440B2 (en) 2010-08-05 2018-05-01 Abbott Point Of Care Inc. Magnetic immunosensor and method of use
US10145843B2 (en) 2010-08-05 2018-12-04 Abbott Point Of Care Inc. Magnetic immunosensor and method of use
RU2566605C2 (ru) * 2010-09-20 2015-10-27 Лайфскен, Инк. Устройство и способ усовершенствованных измерений посредством контрольно-измерительного устройства
US9575027B2 (en) 2010-09-30 2017-02-21 Cilag Gmbh International Systems and methods of discriminating between a control sample and a test fluid using capacitance
WO2012042380A1 (en) 2010-09-30 2012-04-05 Cilag Gmbh International Systems and methods for improved stability of electrochemical sensors
US9347910B2 (en) 2010-09-30 2016-05-24 Cilag Gmbh International Systems and methods for improved stability of electrochemical sensors
US10151724B2 (en) 2010-09-30 2018-12-11 Lifescan Ip Holdings, Llc Systems and methods of discriminating between a control sample and a test fluid using capacitance
US8932445B2 (en) 2010-09-30 2015-01-13 Cilag Gmbh International Systems and methods for improved stability of electrochemical sensors
US8617370B2 (en) 2010-09-30 2013-12-31 Cilag Gmbh International Systems and methods of discriminating between a control sample and a test fluid using capacitance
US9575026B2 (en) 2010-09-30 2017-02-21 Cilag Gmbh International Systems and methods of discriminating between a control sample and a test fluid using capacitance
RU2587501C2 (ru) * 2011-04-20 2016-06-20 Цилаг Гмбх Интернэшнл Электрохимические датчики с полем носителя
US20140027310A1 (en) * 2012-07-27 2014-01-30 Ohmx Corporation Electric measurement of monolayers following pro-cleave detection of presence and activity of enzymes and other target analytes
US9404883B2 (en) 2012-07-27 2016-08-02 Ohmx Corporation Electronic measurements of monolayers following homogeneous reactions of their components
US9416390B2 (en) * 2012-07-27 2016-08-16 Ohmx Corporation Electric measurement of monolayers following pro-cleave detection of presence and activity of enzymes and other target analytes
US20140048724A1 (en) * 2012-08-14 2014-02-20 Strategic Partnerships Alliance, LLC Antiseptic system using ultraviolet rays
US10092669B2 (en) 2012-08-14 2018-10-09 Strategic Partnerships Alliance, LLC Sterilizing radiation system for use with door handle
US20150226735A1 (en) * 2012-09-19 2015-08-13 Universal Biosensors Pty Ltd Systems and methods for enzyme detection
WO2018067468A1 (en) 2016-10-03 2018-04-12 Abbott Laboratories Improved methods of assessing uch-l1 status in patient samples
WO2018067474A1 (en) 2016-10-03 2018-04-12 Abbott Laboratories Improved methods of assessing gfap status in patient samples
EP4521116A2 (en) 2016-10-03 2025-03-12 Abbott Laboratories Improved methods of assessing uch-l1 status in patient samples
WO2018175942A1 (en) 2017-03-23 2018-09-27 Abbott Laboratories Methods for aiding in the diagnosis and determination of the extent of traumatic brain injury in a human subject using the early biomarker ubiquitin carboxy-terminal hydrolase l1
WO2018191531A1 (en) 2017-04-15 2018-10-18 Abbott Laboratories Methods for aiding in the hyperacute diagnosis and determination of traumatic brain injury in a human subject using early biomarkers
WO2018200823A1 (en) 2017-04-28 2018-11-01 Abbott Laboratories Methods for aiding in the hyperacute diagnosis and determination of traumatic brain injury using early biomarkers on at least two samples from the same human subject
WO2018218169A1 (en) 2017-05-25 2018-11-29 Abbott Laboratories Methods for aiding in the determination of whether to perform imaging on a human subject who has sustained or may have sustained an injury to the head using early biomarkers
WO2018222783A1 (en) 2017-05-30 2018-12-06 Abbott Laboratories Methods for aiding in diagnosing and evaluating a mild traumatic brain injury in a human subject using cardiac troponin i and early biomarkers
WO2018222784A1 (en) 2017-05-30 2018-12-06 Abbott Laboratories Methods for aiding in diagnosing and evaluating a mild traumatic brain injury in a human subject using cardiac troponin i
WO2019010131A1 (en) 2017-07-03 2019-01-10 Abbott Laboratories IMPROVED METHODS FOR MEASURING CARBOXY TERMINATION HYDROLASE LEVELS OF UBIQUITIN L1 IN BLOOD
WO2019112860A1 (en) 2017-12-09 2019-06-13 Abbott Laboratories Methods for aiding in diagnosing and evaluating a traumatic brain injury in a human subject using a combination of gfap and uch-l1
WO2019113525A2 (en) 2017-12-09 2019-06-13 Abbott Laboratories Methods for aiding in the diagnosis and evaluation of a subject who has sustained an orthopedic injury and that has or may have sustained an injury to the head, such as mild traumatic brain injury (tbi), using glial fibrillary acidic protein (gfap) and/or ubiquitin carboxy-terminal hydrolase l1 (uch-l1)
WO2019133717A1 (en) 2017-12-29 2019-07-04 Abbott Laboratories Novel biomarkers and methods for diagnosing and evaluating traumatic brain injury
WO2020180695A1 (en) 2019-03-01 2020-09-10 Abbott Laboratories Methods for predicting major adverse cardiovascular events in subjects with coronary artery disease
US11079395B2 (en) 2019-03-01 2021-08-03 Abbott Laboratories Methods for predicting major adverse cardiovascular events in subjects with coronary artery disease
US20220214277A1 (en) * 2020-03-11 2022-07-07 Newton Howard Cartridge-based automated rapid test analyzer
US20220178920A1 (en) * 2020-03-11 2022-06-09 Newton Howard Cartridge-based automated rapid test analyzer
US20220187288A1 (en) * 2020-03-11 2022-06-16 Newton Howard Automated pathogen and antibody rapid test
WO2021211331A1 (en) 2020-04-13 2021-10-21 Abbott Point Of Care Inc. METHODS, COMPLEXES AND KITS FOR DETECTING OR DETERMINING AN AMOUNT OF A ß-CORONAVIRUS ANTIBODY IN A SAMPLE
WO2022029494A1 (en) 2020-08-04 2022-02-10 Abbott Rapid Diagnostics International Unlimited Company Assays for detecting sars-cov-2
WO2022031804A1 (en) 2020-08-04 2022-02-10 Abbott Laboratories Improved methods and kits for detecting sars-cov-2 protein in a sample
US11988671B2 (en) 2020-08-04 2024-05-21 Abbott Rapid Diagnostics International Unlimited Company Assays for detecting SARS-CoV-2
WO2022119841A1 (en) 2020-12-01 2022-06-09 Abbott Laboratories Use of one or more biomarkers to determine traumatic brain injury (tbi) in a subject having received a head computerized tomography scan that is negative for a tbi
WO2022147147A1 (en) 2020-12-30 2022-07-07 Abbott Laboratories Methods for determining sars-cov-2 antigen and anti-sars-cov-2 antibody in a sample
WO2022147178A1 (en) 2020-12-30 2022-07-07 Abbott Laboratories Improved methods, reagents and kits for detergent-based inactivation of betacoronavirus prior to and/or while assessing a biological sample for sars-cov-2 antigen or antibody
WO2022245920A1 (en) 2021-05-18 2022-11-24 Abbott Laboratories Methods of evaluating brain injury in a pediatric subject
WO2022266034A1 (en) 2021-06-14 2022-12-22 Abbott Laboratories Methods of diagnosing or aiding in diagnosis of brain injury caused by acoustic energy, electromagnetic energy, an over pressurization wave, and/or blast wind
EP4528280A2 (en) 2021-06-14 2025-03-26 Abbott Laboratories Methods of diagnosing or aiding in diagnosis of brain injury caused by acoustic energy, electromagnetic energy, an over pressurization wave, and/or blast wind
WO2023028186A1 (en) 2021-08-27 2023-03-02 Abbott Laboratories Methods for detecting immunoglobulin g, subclass 4 (igg4) in a biological sample
WO2023034777A1 (en) 2021-08-31 2023-03-09 Abbott Laboratories Methods and systems of diagnosing brain injury
WO2023056268A1 (en) 2021-09-30 2023-04-06 Abbott Laboratories Methods and systems of diagnosing brain injury
WO2023102384A1 (en) 2021-11-30 2023-06-08 Abbott Laboratories Use of one or more biomarkers to determine traumatic brain injury (tbi) in a subject having received a head computerized tomography scan that is negative for a tbi
WO2023114978A1 (en) 2021-12-17 2023-06-22 Abbott Laboratories Systems and methods for determining uch-l1, gfap, and other biomarkers in blood samples
WO2023129942A1 (en) 2021-12-28 2023-07-06 Abbott Laboratories Use of biomarkers to determine sub-acute traumatic brain injury (tbi) in a subject having received a head computerized tomography (ct) scan that is negative for a tbi or no head ct scan
WO2023154110A1 (en) 2022-02-11 2023-08-17 Abbott Point Of Care Inc. Apparatus and devices for processing fluid samples
WO2024006876A1 (en) 2022-06-29 2024-01-04 Abbott Laboratories Magnetic point-of-care systems and assays for determining gfap in biological samples
WO2024015493A1 (en) 2022-07-14 2024-01-18 Abbott Laboratories Methods and systems for malignancy prediction of indeterminate pulmonary nodules
WO2024044288A1 (en) 2022-08-26 2024-02-29 Abbott Laboratories Use of cardiac troponin and galectin-3 to differentiate myocardial infarction type i and type ii
WO2024059708A1 (en) 2022-09-15 2024-03-21 Abbott Laboratories Biomarkers and methods for differentiating between mild and supermild traumatic brain injury
WO2024102383A1 (en) 2022-11-10 2024-05-16 Abbott Laboratories Methods of identifying macrotroponin in biological samples
WO2024211475A1 (en) 2023-04-04 2024-10-10 Abbott Laboratories Use of biomarkers to determine whether a subject has sustained, may have sustained or is suspected of sustaining a subacute acquired brain injury (abi)
WO2024226971A1 (en) 2023-04-28 2024-10-31 Abbott Point Of Care Inc. Improved assays, cartridges, and kits for detection of biomarkers, including brain injury biomarkers
WO2024226899A1 (en) 2023-04-28 2024-10-31 Abbott Laboratories Diagnosis of late-stage hepatocellular carcinoma
WO2024226969A1 (en) 2023-04-28 2024-10-31 Abbott Point Of Care Inc. Improved assays, cartridges, and kits for detection of biomarkers, including brain injury biomarkers
WO2025145020A2 (en) 2023-12-28 2025-07-03 Abbott Laboratories Methods, systems, compounds, and kits for determining an analyte of interest in a test sample
WO2025193825A1 (en) 2024-03-13 2025-09-18 Abbott Laboratories Diagnosis and monitoring of liver disease
WO2025198859A1 (en) 2024-03-21 2025-09-25 Abbott Laboratories Synthesis of thyroid hormone derivatives and their role as calibrators for thyroid hormone immunoassays
WO2025230857A1 (en) 2024-05-01 2025-11-06 Abbott Laboratories Improved methods for determining cardiac myosin binding protein c in biological samples

Also Published As

Publication number Publication date
CY1113686T1 (el) 2016-06-22
US20100006452A1 (en) 2010-01-14
ES2365169T3 (es) 2011-09-23
EP1788391B1 (en) 2011-05-11
JP2007139781A (ja) 2007-06-07
HK1101765A1 (en) 2007-10-26
ATE509274T1 (de) 2011-05-15
JP5288700B2 (ja) 2013-09-11
PL1788391T3 (pl) 2011-10-31
CN1975421A (zh) 2007-06-06
DK1788391T3 (da) 2011-08-29
EP2259062A2 (en) 2010-12-08
SI1788391T1 (sl) 2011-09-30
US9863942B2 (en) 2018-01-09
EP2259062A3 (en) 2011-10-12
PT1788391E (pt) 2011-07-15
EP1788391A1 (en) 2007-05-23

Similar Documents

Publication Publication Date Title
US9863942B2 (en) Biosensor apparatus and methods of use
US8951749B2 (en) Enhanced immunoassay sensor
US9939440B2 (en) Electrochemical analyte detection apparatus and method
CA2415602C (en) Immunosensor
EP2205357B1 (en) Assay device and method
US8685714B2 (en) Immunosensor
HK1151589A (en) Biosensor apparatus and methods of use
HK1101765B (en) Biosensor apparatus and methods of use
HK1157274B (en) Enhanced immunoassay sensor
HK1141753B (en) Assay device and method
HK1141753A (en) Assay device and method

Legal Events

Date Code Title Description
AS Assignment

Owner name: LIFESCAN, INC., CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:RYLATT, DENNIS;HODGES, ALASTAIR;CHATELIER, RONALD;REEL/FRAME:017631/0451

Effective date: 20060210

AS Assignment

Owner name: UNIVERSAL BIOSENSORS PTY LTD., AUSTRALIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:LIFESCAN, INC.;REEL/FRAME:021461/0755

Effective date: 20080828

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION