US20110312802A1 - Test module with probes suspended in fluid - Google Patents

Test module with probes suspended in fluid Download PDF

Info

Publication number
US20110312802A1
US20110312802A1 US13150228 US201113150228A US2011312802A1 US 20110312802 A1 US20110312802 A1 US 20110312802A1 US 13150228 US13150228 US 13150228 US 201113150228 A US201113150228 A US 201113150228A US 2011312802 A1 US2011312802 A1 US 2011312802A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
fig
amplification
hybridization
loc
nucleic
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
US13150228
Inventor
Kia Silverbrook
Mehdi Azimi
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.)
Geneasys Pty Ltd
Original Assignee
Geneasys Pty Ltd
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

Links

Images

Classifications

    • CCHEMISTRY; METALLURGY
    • C12BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12QMEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/68Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving nucleic acids
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/502707Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by the manufacture of the container or its components
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/502738Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by integrated valves
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16KVALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
    • F16K99/00Subject matter not provided for in other groups of this subclass
    • F16K99/0001Microvalves
    • F16K99/0003Constructional types of microvalves; Details of the cutting-off member
    • F16K99/003Valves for single use only
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16KVALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
    • F16K99/00Subject matter not provided for in other groups of this subclass
    • F16K99/0001Microvalves
    • F16K99/0034Operating means specially adapted for microvalves
    • F16K99/0036Operating means specially adapted for microvalves operated by temperature variations
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2200/00Solutions for specific problems relating to chemical or physical laboratory apparatus
    • B01L2200/10Integrating sample preparation and analysis in single entity, e.g. lab-on-a-chip concept
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00Additional constructional details
    • B01L2300/02Identification, exchange or storage of information
    • B01L2300/023Sending and receiving of information, e.g. using bluetooth
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00Additional constructional details
    • B01L2300/02Identification, exchange or storage of information
    • B01L2300/024Storing results with means integrated into the container
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00Additional constructional details
    • B01L2300/06Auxiliary integrated devices, integrated components
    • B01L2300/0627Sensor or part of a sensor is integrated
    • B01L2300/0636Integrated biosensor, microarrays
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00Additional constructional details
    • B01L2300/06Auxiliary integrated devices, integrated components
    • B01L2300/0627Sensor or part of a sensor is integrated
    • B01L2300/0654Lenses; Optical fibres
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00Additional constructional details
    • B01L2300/08Geometry, shape and general structure
    • B01L2300/0861Configuration of multiple channels and/or chambers in a single devices
    • B01L2300/0883Serpentine channels
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00Additional constructional details
    • B01L2300/10Means to control humidity and/or other gases
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00Additional constructional details
    • B01L2300/18Means for temperature control
    • B01L2300/1805Conductive heating, heat from thermostatted solids is conducted to receptacles, e.g. heating plates, blocks
    • B01L2300/1827Conductive heating, heat from thermostatted solids is conducted to receptacles, e.g. heating plates, blocks using resistive heater
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00Moving or stopping fluids
    • B01L2400/04Moving fluids with specific forces or mechanical means
    • B01L2400/0403Moving fluids with specific forces or mechanical means specific forces
    • B01L2400/0406Moving fluids with specific forces or mechanical means specific forces capillary forces
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00Moving or stopping fluids
    • B01L2400/06Valves, specific forms thereof
    • B01L2400/0633Valves, specific forms thereof with moving parts
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00Moving or stopping fluids
    • B01L2400/06Valves, specific forms thereof
    • B01L2400/0677Valves, specific forms thereof phase change valves; Meltable, freezing, dissolvable plugs; Destructible barriers
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00Moving or stopping fluids
    • B01L2400/06Valves, specific forms thereof
    • B01L2400/0688Valves, specific forms thereof surface tension valves, capillary stop, capillary break
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01LCHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L7/00Heating or cooling apparatus; Heat insulating devices
    • B01L7/52Heating or cooling apparatus; Heat insulating devices with provision for submitting samples to a predetermined sequence of different temperatures, e.g. for treating nucleic acid samples
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/0318Processes
    • Y10T137/0324With control of flow by a condition or characteristic of a fluid
    • Y10T137/0329Mixing of plural fluids of diverse characteristics or conditions
    • Y10T137/0352Controlled by pressure
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/0318Processes
    • Y10T137/0391Affecting flow by the addition of material or energy
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/0971Speed responsive valve control
    • Y10T137/1044With other condition responsive valve control
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/206Flow affected by fluid contact, energy field or coanda effect [e.g., pure fluid device or system]
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/206Flow affected by fluid contact, energy field or coanda effect [e.g., pure fluid device or system]
    • Y10T137/2076Utilizing diverse fluids
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T137/00Fluid handling
    • Y10T137/206Flow affected by fluid contact, energy field or coanda effect [e.g., pure fluid device or system]
    • Y10T137/218Means to regulate or vary operation of device
    • Y10T137/2202By movable element
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/10Composition for standardization, calibration, simulation, stabilization, preparation or preservation; processes of use in preparation for chemical testing
    • Y10T436/107497Preparation composition [e.g., lysing or precipitation, etc.]
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/11Automated chemical analysis
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/14Heterocyclic carbon compound [i.e., O, S, N, Se, Te, as only ring hetero atom]
    • Y10T436/142222Hetero-O [e.g., ascorbic acid, etc.]
    • Y10T436/143333Saccharide [e.g., DNA, etc.]
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/14Heterocyclic carbon compound [i.e., O, S, N, Se, Te, as only ring hetero atom]
    • Y10T436/145555Hetero-N
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/17Nitrogen containing
    • Y10T436/173845Amine and quaternary ammonium
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/20Oxygen containing
    • Y10T436/203332Hydroxyl containing
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/25Chemistry: analytical and immunological testing including sample preparation
    • YGENERAL 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
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T436/00Chemistry: analytical and immunological testing
    • Y10T436/25Chemistry: analytical and immunological testing including sample preparation
    • Y10T436/25375Liberation or purification of sample or separation of material from a sample [e.g., filtering, centrifuging, etc.]

Abstract

A test module having an outer casing having an inlet for receiving a biological sample containing a target nucleic acid sequence, and, probes in the outer casing for hybridization with the target nucleic acid sequence to form probe-target hybrids, the probes each having a fluorophore such that the probe-target hybrids emit a fluorescence signal in response to exposure to an excitation light, wherein, the probes are suspended in a fluid.

Description

    FIELD OF THE INVENTION
  • [0001]
    The present invention relates to diagnostic devices that use microsystems technologies (MST). In particular, the invention relates to microfluidic and biochemical processing and analysis for molecular diagnostics.
  • CO-PENDING APPLICATIONS
  • [0002]
    The following applications have been filed by the Applicant which relate to the present application:
  • [0000]
    GBS001US GBS002US GBS003US GBS005US GBS006US
    GSR001US GSR002US GAS001US GAS002US GAS003US
    GAS004US GAS006US GAS007US GAS008US GAS009US
    GAS010US GAS012US GAS013US GAS014US GAS015US
    GAS016US GAS017US GAS018US GAS019US GAS020US
    GAS021US GAS022US GAS023US GAS024US GAS025US
    GAS026US GAS027US GAS028US GAS030US GAS031US
    GAS032US GAS033US GAS034US GAS035US GAS036US
    GAS037US GAS038US GAS039US GAS040US GAS041US
    GAS042US GAS043US GAS044US GAS045US GAS046US
    GAS047US GAS048US GAS049US GAS050US GAS054US
    GAS055US GAS056US GAS057US GAS059US GAS060US
    GAS061US GAS062US GAS063US GAS065US GAS066US
    GAS067US GAS068US GAS069US GAS070US GAS080US
    GAS081US GAS082US GAS083US GAS084US GAS085US
    GAS086US GAS087US GAS088US GAS089US GAS090US
    GAS091US GAS092US GAS093US GAS094US GAS095US
    GAS096US GAS097US GAS098US GAS099US GAS100US
    GAS101US GAS102US GAS103US GAS104US GAS105US
    GAS106US GAS108US GAS109US GAS110US GAS111US
    GAS112US GAS113US GAS114US GAS115US GAS117US
    GAS118US GAS119US GAS120US GAS121US GAS122US
    GAS123US GAS124US GAS125US GAS126US GAS127US
    GAS128US GAS129US GAS130US GAS131US GAS132US
    GAS133US GAS134US GAS135US GAS136US GAS137US
    GAS138US GAS139US GAS140US GAS141US GAS142US
    GAS143US GAS144US GAS146US GAS147US GRR001US
    GRR002US GRR003US GRR004US GRR005US GRR006US
    GRR007US GRR008US GRR009US GRR010US GVA001US
    GVA002US GVA004US GVA005US GVA006US GVA007US
    GVA008US GVA009US GVA010US GVA011US GVA012US
    GVA013US GVA014US GVA015US GVA016US GVA017US
    GVA018US GVA019US GVA020US GVA021US GVA022US
    GHU001US GHU002US GHU003US GHU004US GHU006US
    GHU007US GHU008US GWM001US GWM002US GDI001US
    GDI002US GDI003US GDI004US GDI005US GDI006US
    GDI007US GDI009US GDI010US GDI011US GDI013US
    GDI014US GDI015US GDI016US GDI017US GDI019US
    GDI023US GDI028US GDI030US GDI039US GDI040US
    GDI041US GPC001US GPC002US GPC003US GPC004US
    GPC005US GPC006US GPC007US GPC008US GPC009US
    GPC010US GPC011US GPC012US GPC014US GPC017US
    GPC018US GPC019US GPC023US GPC027US GPC028US
    GPC029US GPC030US GPC031US GPC033US GPC034US
    GPC035US GPC036US GPC037US GPC038US GPC039US
    GPC040US GPC041US GPC042US GPC043US GLY001US
    GLY002US GLY003US GLY004US GLY005US GLY006US
    GIN001US GIN002US GIN003US GIN004US GIN005US
    GIN006US GIN007US GIN008US GMI001US GMI002US
    GMI005US GMI008US GLE001US GLE002US GLE003US
    GLE004US GLE005US GLE006US GLE007US GLE008US
    GLE009US GLE010US GLE011US GLE012US GLE013US
    GLE014US GLA001US GGA001US GGA003US GRE001US
    GRE002US GRE003US GRE004US GRE005US GRE006US
    GRE007US GCF001US GCF002US GCF003US GCF004US
    GCF005US GCF006US GCF007US GCF008US GCF009US
    GCF010US GCF011US GCF012US GCF013US GCF014US
    GCF015US GCF016US GCF020US GCF021US GCF022US
    GCF023US GCF024US GCF025US GCF027US GCF028US
    GCF029US GCF030US GCF031US GCF032US GCF033US
    GCF034US GCF035US GCF036US GCF037US GSA001US
    GSA002US GSE001US GSE002US GSE003US GSE004US
    GDA001US GDA002US GDA003US GDA004US GDA005US
    GDA006US GDA007US GPK001US GMO001US GMV001US
    GMV002US GMV003US GMV004US GRD001US GRD002US
    GRD003US GRD004US GPD001US GPD003US GPD004US
    GPD005US GPD006US GPD007US GPD008US GPD009US
    GPD010US GPD011US GPD012US GPD013US GPD014US
    GPD015US GPD016US GPD017US GAL001US GPA001US
    GPA003US GPA004US GPA005US GSS001US GSL001US
    GCA001US GCA002US GCA003US
  • [0003]
    The disclosures of these co-pending applications are incorporated herein by reference. The above applications have been identified by their filing docket number, which will be substituted with the corresponding application number, once assigned.
  • BACKGROUND OF THE INVENTION
  • [0004]
    Molecular diagnostics has emerged as a field that offers the promise of early disease detection, potentially before symptoms have manifested. Molecular diagnostic testing is used to detect:
      • Inherited disorders
      • Acquired disorders
      • Infectious diseases
      • Genetic predisposition to health-related conditions.
      • With high accuracy and fast turnaround times, molecular diagnostic tests have the potential to reduce the occurrence of ineffective health care services, enhance patient outcomes, improve disease management and individualize patient care. Many of the techniques in molecular diagnostics are based on the detection and identification of specific nucleic acids, both deoxyribonucleic acid (DNA) and ribonucleic acid (RNA), extracted and amplified from a biological specimen (such as blood or saliva). The complementary nature of the nucleic acid bases allows short sequences of synthesized DNA (oligonucleotides) to bond (hybridize) to specific nucleic acid sequences for use in nucleic acid tests. If hybridization occurs, then the complementary sequence is present in the sample. This makes it possible, for example, to predict the disease a person will contract in the future, determine the identity and virulence of an infectious pathogen, or determine the response a person will have to a drug.
    Nucleic Acid Based Molecular Diagnostic Test
  • [0010]
    A nucleic acid based test has four distinct steps:
  • [0011]
    1. Sample preparation
  • [0012]
    2. Nucleic acid extraction
  • [0013]
    3. Nucleic acid amplification (optional)
  • [0014]
    4. Detection
  • [0015]
    Many sample types are used for genetic analysis, such as blood, urine, sputum and tissue samples. The diagnostic test determines the type of sample required as not all samples are representative of the disease process. These samples have a variety of constituents, but usually only one of these is of interest. For example, in blood, high concentrations of erythrocytes can inhibit the detection of a pathogenic organism. Therefore a purification and/or concentration step at the beginning of the nucleic acid test is often required.
  • [0016]
    Blood is one of the more commonly sought sample types. It has three major constituents: leukocytes (white blood cells), erythrocytes (red blood cells) and thrombocytes (platelets). The thrombocytes facilitate clotting and remain active in vitro. To inhibit coagulation, the specimen is mixed with an agent such as ethylenediaminetetraacetic acid (EDTA) prior to purification and concentration. Erythrocytes are usually removed from the sample in order to concentrate the target cells. In humans, erythrocytes account for approximately 99% of the cellular material but do not carry DNA as they have no nucleus. Furthermore, erythrocytes contain components such as haemoglobin that can interfere with the downstream nucleic acid amplification process (described below). Removal of erythrocytes can be achieved by differentially lysing the erythrocytes in a lysis solution, leaving remaining cellular material intact which can then be separated from the sample using centrifugation. This provides a concentration of the target cells from which the nucleic acids are extracted.
  • [0017]
    The exact protocol used to extract nucleic acids depends on the sample and the diagnostic assay to be performed. For example, the protocol for extracting viral RNA will vary considerably from the protocol to extract genomic DNA. However, extracting nucleic acids from target cells usually involves a cell lysis step followed by nucleic acid purification. The cell lysis step disrupts the cell and nuclear membranes, releasing the genetic material. This is often accomplished using a lysis detergent, such as sodium dodecyl sulfate, which also denatures the large amount of proteins present in the cells.
  • [0018]
    The nucleic acids are then purified with an alcohol precipitation step, usually ice-cold ethanol or isopropanol, or via a solid phase purification step, typically on a silica matrix in a column, resin or on paramagnetic beads in the presence of high concentrations of a chaotropic salt, prior to washing and then elution in a low ionic strength buffer. An optional step prior to nucleic acid precipitation is the addition of a protease which digests the proteins in order to further purify the sample.
  • [0019]
    Other lysis methods include mechanical lysis via ultrasonic vibration and thermal lysis where the sample is heated to 94° C. to disrupt cell membranes.
  • [0020]
    The target DNA or RNA may be present in the extracted material in very small amounts, particularly if the target is of pathogenic origin. Nucleic acid amplification provides the ability to selectively amplify (that is, replicate) specific targets present in low concentrations to detectable levels.
  • [0021]
    The most commonly used nucleic acid amplification technique is the polymerase chain reaction (PCR). PCR is well known in this field and comprehensive description of this type of reaction is provided in E. van Pelt-Verkuil et al., Principles and Technical Aspects of PCR Amplification, Springer, 2008.
  • [0022]
    PCR is a powerful technique that amplifies a target DNA sequence against a background of complex DNA. If RNA is to be amplified (by PCR), it must be first transcribed into cDNA (complementary DNA) using an enzyme called reverse transcriptase. Afterwards, the resulting cDNA is amplified by PCR.
  • [0023]
    PCR is an exponential process that proceeds as long as the conditions for sustaining the reaction are acceptable. The components of the reaction are:
  • [0024]
    1. pair of primers—short single strands of DNA with around 10-30 nucleotides complementary to the regions flanking the target sequence
  • [0025]
    2. DNA polymerase—a thermostable enzyme that synthesizes DNA
  • [0026]
    3. deoxyribonucleoside triphosphates (dNTPs)—provide the nucleotides that are incorporated into the newly synthesized DNA strand
  • [0027]
    4. buffer—to provide the optimal chemical environment for DNA synthesis
  • [0028]
    PCR typically involves placing these reactants in a small tube (˜10-50 microlitres) containing the extracted nucleic acids. The tube is placed in a thermal cycler; an instrument that subjects the reaction to a series of different temperatures for varying amounts of time. The standard protocol for each thermal cycle involves a denaturation phase, an annealing phase, and an extension phase. The extension phase is sometimes referred to as the primer extension phase. In addition to such three-step protocols, two-step thermal protocols can be employed, in which the annealing and extension phases are combined. The denaturation phase typically involves raising the temperature of the reaction to 90-95° C. to denature the DNA strands; in the annealing phase, the temperature is lowered to ˜50-60° C. for the primers to anneal; and then in the extension phase the temperature is raised to the optimal DNA polymerase activity temperature of 60-72° C. for primer extension. This process is repeated cyclically around 20-40 times, the end result being the creation of millions of copies of the target sequence between the primers.
  • [0029]
    There are a number of variants to the standard PCR protocol such as multiplex PCR, linker-primed PCR, direct PCR, tandem PCR, real-time PCR and reverse-transcriptase PCR, amongst others, which have been developed for molecular diagnostics.
  • [0030]
    Multiplex PCR uses multiple primer sets within a single PCR mixture to produce amplicons of varying sizes that are specific to different DNA sequences. By targeting multiple genes at once, additional information may be gained from a single test-run that otherwise would require several experiments. Optimization of multiplex PCR is more difficult though and requires selecting primers with similar annealing temperatures, and amplicons with similar lengths and base composition to ensure the amplification efficiency of each amplicon is equivalent.
  • [0031]
    Linker-primed PCR, also known as ligation adaptor PCR, is a method used to enable nucleic acid amplification of essentially all DNA sequences in a complex DNA mixture without the need for target-specific primers. The method firstly involves digesting the target DNA population with a suitable restriction endonuclease (enzyme). Double-stranded oligonucleotide linkers (also called adaptors) with a suitable overhanging end are then ligated to the ends of target DNA fragments using a ligase enzyme. Nucleic acid amplification is subsequently performed using oligonucleotide primers which are specific for the linker sequences. In this way, all fragments of the DNA source which are flanked by linker oligonucleotides can be amplified.
  • [0032]
    Direct PCR describes a system whereby PCR is performed directly on a sample without any, or with minimal, nucleic acid extraction. It has long been accepted that PCR reactions are inhibited by the presence of many components of unpurified biological samples, such as the haem component in blood. Traditionally, PCR has required extensive purification of the target nucleic acid prior to preparation of the reaction mixture. With appropriate changes to the chemistry and sample concentration, however, it is possible to perform PCR with minimal DNA purification, or direct PCR. Adjustments to the PCR chemistry for direct PCR include increased buffer strength, the use of polymerases which have high activity and processivity, and additives which chelate with potential polymerase inhibitors.
  • [0033]
    Tandem PCR utilises two distinct rounds of nucleic acid amplification to increase the probability that the correct amplicon is amplified. One form of tandem PCR is nested PCR in which two pairs of PCR primers are used to amplify a single locus in separate rounds of nucleic acid amplification. The first pair of primers hybridize to the nucleic acid sequence at regions external to the target nucleic acid sequence. The second pair of primers (nested primers) used in the second round of amplification bind within the first PCR product and produce a second PCR product containing the target nucleic acid, that will be shorter than the first one. The logic behind this strategy is that if the wrong locus were amplified by mistake during the first round of nucleic acid amplification, the probability is very low that it would also be amplified a second time by a second pair of primers and thus ensures specificity.
  • [0034]
    Real-time PCR, or quantitative PCR, is used to measure the quantity of a PCR product in real time. By using a fluorophore-containing probe or fluorescent dyes along with a set of standards in the reaction, it is possible to quantitate the starting amount of nucleic acid in the sample. This is particularly useful in molecular diagnostics where treatment options may differ depending on the pathogen load in the sample.
  • [0035]
    Reverse-transcriptase PCR (RT-PCR) is used to amplify DNA from RNA. Reverse transcriptase is an enzyme that reverse transcribes RNA into complementary DNA (cDNA), which is then amplified by PCR. RT-PCR is widely used in expression profiling, to determine the expression of a gene or to identify the sequence of an RNA transcript, including transcription start and termination sites. It is also used to amplify RNA viruses such as human immunodeficiency virus or hepatitis C virus.
  • [0036]
    Isothermal amplification is another form of nucleic acid amplification which does not rely on the thermal denaturation of the target DNA during the amplification reaction and hence does not require sophisticated machinery. Isothermal nucleic acid amplification methods can therefore be carried out in primitive sites or operated easily outside of a laboratory environment. A number of isothermal nucleic acid amplification methods have been described, including Strand Displacement Amplification, Transcription Mediated Amplification, Nucleic Acid Sequence Based Amplification, Recombinase Polymerase Amplification, Rolling Circle Amplification, Ramification Amplification, Helicase-Dependent Isothermal DNA Amplification and Loop-Mediated Isothermal Amplification.
  • [0037]
    Isothermal nucleic acid amplification methods do not rely on the continuing heat denaturation of the template DNA to produce single stranded molecules to serve as templates for further amplification, but instead rely on alternative methods such as enzymatic nicking of DNA molecules by specific restriction endonucleases, or the use of an enzyme to separate the DNA strands, at a constant temperature.
  • [0038]
    Strand Displacement Amplification (SDA) relies on the ability of certain restriction enzymes to nick the unmodified strand of hemi-modified DNA and the ability of a 5′-3′ exonuclease-deficient polymerase to extend and displace the downstream strand. Exponential nucleic acid amplification is then achieved by coupling sense and antisense reactions in which strand displacement from the sense reaction serves as a template for the antisense reaction. The use of nickase enzymes which do not cut DNA in the traditional manner but produce a nick on one of the DNA strands, such as N. A1w1, N. BstNB1 and M1y1, are useful in this reaction. SDA has been improved by the use of a combination of a heat-stable restriction enzyme (Ava1) and heat-stable Exo-polymerase (Bst polymerase). This combination has been shown to increase amplification efficiency of the reaction from 108 fold amplification to 1010 fold amplification so that it is possible using this technique to amplify unique single copy molecules.
  • [0039]
    Transcription Mediated Amplification (TMA) and Nucleic Acid Sequence Based Amplification (NASBA) use an RNA polymerase to copy RNA sequences but not corresponding genomic DNA. The technology uses two primers and two or three enzymes, RNA polymerase, reverse transcriptase and optionally RNase H (if the reverse transcriptase does not have RNase activity). One primer contains a promoter sequence for RNA polymerase. In the first step of nucleic acid amplification, this primer hybridizes to the target ribosomal RNA (rRNA) at a defined site. Reverse transcriptase creates a DNA copy of the target rRNA by extension from the 3′ end of the promoter primer. The RNA in the resulting RNA:DNA duplex is degraded by the RNase activity of the reverse transcriptase if present or the additional RNase H. Next, a second primer binds to the DNA copy. A new strand of DNA is synthesized from the end of this primer by reverse transcriptase, creating a double-stranded DNA molecule. RNA polymerase recognizes the promoter sequence in the DNA template and initiates transcription. Each of the newly synthesized RNA amplicons re-enters the process and serves as a template for a new round of replication.
  • [0040]
    In Recombinase Polymerase Amplification (RPA), the isothermal amplification of specific DNA fragments is achieved by the binding of opposing oligonucleotide primers to template DNA and their extension by a DNA polymerase. Heat is not required to denature the double-stranded DNA (dsDNA) template. Instead, RPA employs recombinase-primer complexes to scan dsDNA and facilitate strand exchange at cognate sites. The resulting structures are stabilised by single-stranded DNA binding proteins interacting with the displaced template strand, thus preventing the ejection of the primer by branch migration. Recombinase disassembly leaves the 3′ end of the oligonucleotide accessible to a strand displacing DNA polymerase, such as the large fragment of Bacillus subtilis Pol I (Bsu), and primer extension ensues. Exponential nucleic acid amplification is accomplished by the cyclic repetition of this process.
  • [0041]
    Helicase-dependent amplification (HDA) mimics the in vivo system in that it uses a DNA helicase enzyme to generate single-stranded templates for primer hybridization and subsequent primer extension by a DNA polymerase. In the first step of the HDA reaction, the helicase enzyme traverses along the target DNA, disrupting the hydrogen bonds linking the two strands which are then bound by single-stranded binding proteins. Exposure of the single-stranded target region by the helicase allows primers to anneal. The DNA polymerase then extends the 3′ ends of each primer using free deoxyribonucleoside triphosphates (dNTPs) to produce two DNA replicates. The two replicated dsDNA strands independently enter the next cycle of HDA, resulting in exponential nucleic acid amplification of the target sequence.
  • [0042]
    Other DNA-based isothermal techniques include Rolling Circle Amplification (RCA) in which a DNA polymerase extends a primer continuously around a circular DNA template, generating a long DNA product that consists of many repeated copies of the circle. By the end of the reaction, the polymerase generates many thousands of copies of the circular template, with the chain of copies tethered to the original target DNA. This allows for spatial resolution of target and rapid nucleic acid amplification of the signal. Up to 1012 copies of template can be generated in 1 hour. Ramification amplification is a variation of RCA and utilizes a closed circular probe (C-probe) or padlock probe and a DNA polymerase with a high processivity to exponentially amplify the C-probe under isothermal conditions.
  • [0043]
    Loop-mediated isothermal amplification (LAMP), offers high selectivity and employs a DNA polymerase and a set of four specially designed primers that recognize a total of six distinct sequences on the target DNA. An inner primer containing sequences of the sense and antisense strands of the target DNA initiates LAMP. The following strand displacement DNA synthesis primed by an outer primer releases a single-stranded DNA. This serves as template for DNA synthesis primed by the second inner and outer primers that hybridize to the other end of the target, which produces a stem-loop DNA structure. In subsequent LAMP cycling one inner primer hybridizes to the loop on the product and initiates displacement DNA synthesis, yielding the original stem-loop DNA and a new stem-loop DNA with a stem twice as long. The cycling reaction continues with accumulation of 109 copies of target in less than an hour. The final products are stem-loop DNAs with several inverted repeats of the target and cauliflower-like structures with multiple loops formed by annealing between alternately inverted repeats of the target in the same strand.
  • [0044]
    After completion of the nucleic acid amplification, the amplified product must be analysed to determine whether the anticipated amplicon (the amplified quantity of target nucleic acids) was generated. The methods of analyzing the product range from simply determining the size of the amplicon through gel electrophoresis, to identifying the nucleotide composition of the amplicon using DNA hybridization.
  • [0045]
    Gel electrophoresis is one of the simplest ways to check whether the nucleic acid amplification process generated the anticipated amplicon. Gel electrophoresis uses an electric field applied to a gel matrix to separate DNA fragments. The negatively charged DNA fragments will move through the matrix at different rates, determined largely by their size. After the electrophoresis is complete, the fragments in the gel can be stained to make them visible. Ethidium bromide is a commonly used stain which fluoresces under UV light.
  • [0046]
    The size of the fragments is determined by comparison with a DNA size marker (a DNA ladder), which contains DNA fragments of known sizes, run on the gel alongside the amplicon. Because the oligonucleotide primers bind to specific sites flanking the target DNA, the size of the amplified product can be anticipated and detected as a band of known size on the gel. To be certain of the identity of the amplicon, or if several amplicons have been generated, DNA probe hybridization to the amplicon is commonly employed.
  • [0047]
    DNA hybridization refers to the formation of double-stranded DNA by complementary base pairing. DNA hybridization for positive identification of a specific amplification product requires the use of a DNA probe around 20 nucleotides in length. If the probe has a sequence that is complementary to the amplicon (target) DNA sequence, hybridization will occur under favourable conditions of temperature, pH and ionic concentration. If hybridization occurs, then the gene or DNA sequence of interest was present in the original sample.
  • [0048]
    Optical detection is the most common method to detect hybridization. Either the amplicons or the probes are labelled to emit light through fluorescence or electrochemiluminescence. These processes differ in the means of producing excited states of the light-producing moieties, but both enable covalent labelling of nucleotide strands. In electrochemiluminescence (ECL), light is produced by luminophore molecules or complexes upon stimulation with an electric current. In fluorescence, it is illumination with excitation light which leads to emission.
  • [0049]
    Fluorescence is detected using an illumination source which provides excitation light at a wavelength absorbed by the fluorescent molecule, and a detection unit. The detection unit comprises a photosensor (such as a photomultiplier tube or charge-coupled device (CCD) array) to detect the emitted signal, and a mechanism (such as a wavelength-selective filter) to prevent the excitation light from being included in the photosensor output. The fluorescent molecules emit Stokes-shifted light in response to the excitation light, and this emitted light is collected by the detection unit. Stokes shift is the frequency difference or wavelength difference between emitted light and absorbed excitation light.
  • [0050]
    ECL emission is detected using a photosensor which is sensitive to the emission wavelength of the ECL species being employed. For example, transition metal-ligand complexes emit light at visible wavelengths, so conventional photodiodes and CCDs are employed as photosensors. An advantage of ECL is that, if ambient light is excluded, the ECL emission can be the only light present in the detection system, which improves sensitivity.
  • [0051]
    Microarrays allow for hundreds of thousands of DNA hybridization experiments to be performed simultaneously. Microarrays are powerful tools for molecular diagnostics with the potential to screen for thousands of genetic diseases or detect the presence of numerous infectious pathogens in a single test. A microarray consists of many different DNA probes immobilized as spots on a substrate. The target DNA (amplicon) is first labelled with a fluorescent or luminescent molecule (either during or after nucleic acid amplification) and then applied to the array of probes. The microarray is incubated in a temperature controlled, humid environment for a number of hours or days while hybridization between the probe and amplicon takes place. Following incubation, the microarray must be washed in a series of buffers to remove unbound strands. Once washed, the microarray surface is dried using a stream of air (often nitrogen). The stringency of the hybridization and washes is critical. Insufficient stringency can result in a high degree of nonspecific binding. Excessive stringency can lead to a failure of appropriate binding, which results in diminished sensitivity. Hybridization is recognized by detecting light emission from the labelled amplicons which have formed a hybrid with complementary probes.
  • [0052]
    Fluorescence from microarrays is detected using a microarray scanner which is generally a computer controlled inverted scanning fluorescence confocal microscope which typically uses a laser for excitation of the fluorescent dye and a photosensor (such as a photomultiplier tube or CCD) to detect the emitted signal. The fluorescent molecules emit Stokes-shifted light (described above) which is collected by the detection unit.
  • [0053]
    The emitted fluorescence must be collected, separated from the unabsorbed excitation wavelength, and transported to the detector. In microarray scanners, a confocal arrangement is commonly used to eliminate out-of-focus information by means of a confocal pinhole situated at an image plane. This allows only the in-focus portion of the light to be detected. Light from above and below the plane of focus of the object is prevented from entering the detector, thereby increasing the signal to noise ratio. The detected fluorescent photons are converted into electrical energy by the detector which is subsequently converted to a digital signal. This digital signal translates to a number representing the intensity of fluorescence from a given pixel. Each feature of the array is made up of one or more such pixels. The final result of a scan is an image of the array surface. The exact sequence and position of every probe on the microarray is known, and so the hybridized target sequences can be identified and analysed simultaneously.
  • [0054]
    More information regarding fluorescent probes can be found at: http://www. premierbiosoft. com/tech_notes/FRET_probe. html and http://www. invitrogen. com/site/us/en/home/References/Molecular-Probes-The-Handbook/Technical-Notes-and-Product-Highlights/Fluorescence-Resonance-Energy-Transfer-FRET. html
  • Point-of-Care Molecular Diagnostics
  • [0055]
    Despite the advantages that molecular diagnostic tests offer, the growth of this type of testing in the clinical laboratory has been slower than expected and remains a minor part of the practice of laboratory medicine. This is primarily due to the complexity and costs associated with nucleic acid testing compared with tests based on methods not involving nucleic acids. The widespread adaptation of molecular diagnostics testing to the clinical setting is intimately tied to the development of instrumentation that significantly reduces the cost, provides a rapid and automated assay from start (specimen processing) to finish (generating a result) and operates without major intervention by personnel.
  • [0056]
    A point-of-care technology serving the physician's office, the hospital bedside or even consumer-based, at home, would offer many advantages including:
      • rapid availability of results enabling immediate facilitation of treatment and improved quality of care.
      • ability to obtain laboratory values from testing very small samples.
      • reduced clinical workload.
      • reduced laboratory workload and improved office efficiency by reducing administrative work.
      • improved cost per patient through reduced length of stay of hospitalization, conclusion of outpatient consultation at the first visit, and reduced handling, storing and shipping of specimens.
      • facilitation of clinical management decisions such as infection control and antibiotic use.
    Lab-on-a-Chip (LOC) Based Molecular Diagnostics
  • [0063]
    Molecular diagnostic systems based on microfluidic technologies provide the means to automate and speed up molecular diagnostic assays. The quicker detection times are primarily due to the extremely low volumes involved, automation, and the low-overhead inbuilt cascading of the diagnostic process steps within a microfluidic device. Volumes in the nanoliter and microliter scale also reduce reagent consumption and cost. Lab-on-a-chip (LOC) devices are a common form of microfluidic device. LOC devices have MST structures within a MST layer for fluid processing integrated onto a single supporting substrate (usually silicon). Fabrication using the VLSI (very large scale integrated) lithographic techniques of the semiconductor industry keeps the unit cost of each LOC device very low. However, controlling fluid flow through the LOC device, adding reagents, controlling reaction conditions and so on necessitate bulky external plumbing and electronics. Connecting a LOC device to these external devices effectively restricts the use of LOC devices for molecular diagnostics to the laboratory setting. The cost of the external equipment and complexity of its operation precludes LOC-based molecular diagnostics as a practical option for point-of-care settings.
  • [0064]
    In view of the above, there is a need for a molecular diagnostic system based on a LOC device for use at point-of-care.
  • SUMMARY OF THE INVENTION
  • [0065]
    Accordingly, the present invention provides a test module comprising:
  • [0066]
    an outer casing having an inlet for receiving a biological sample containing a target nucleic acid sequence; and,
  • [0067]
    probes in the outer casing for hybridization with the target nucleic acid sequence to form probe-target hybrids, the probes each having a fluorophore such that the probe-target hybrids emit a fluorescence signal in response to exposure to an excitation light; wherein,
  • [0068]
    the probes are suspended in a fluid.
  • [0069]
    Preferably, the mass of the probes is less than 270 picograms.
  • [0070]
    Preferably, the test module also has a hybridization chamber mounted in the casing for containing probes wherein the hybridization chamber has a volume less than 9,000 cubic microns.
  • [0071]
    Preferably, and the hybridization chamber has an optical window for exposing the probes to the excitation light.
  • [0072]
    Preferably, the test module also has a light source for generating the excitation light and a photodiode for sensing the fluorescent response.
  • [0073]
    Preferably, the light source is an excitation LED mounted in the casing for emitting light through the optical window.
  • [0074]
    Preferably, the test module also has control circuitry for operative control of the excitation LED.
  • [0075]
    Preferably, the control circuitry controls activation and deactivation of the excitation LED, and conditioning of power supplied to the excitation light.
  • [0076]
    Preferably, the control circuitry is configured to deactivate the excitation light and subsequently activate the photodiode after a time delay.
  • [0077]
    Preferably, the test module also has a shunt transistor between the photodiode anode and a voltage source, the shunt transistor being configured to remove carriers generated by absorption of photons of the excitation light in the photodiode.
  • [0078]
    Preferably, the shunt transistor is configured to turn on when the excitation light activates and turn off when the excitation light deactivates.
  • [0079]
    Preferably, the test module also has an array of hybridization chambers containing different types of the probes, the probes being fluorescence resonance energy transfer (FRET) probes configured for hybridization with different target nucleic acid sequences, and an array of the photodiodes such that each of the hybridization chambers corresponds to a respective one of the photodiodes.
  • [0080]
    Preferably, the test module also has a polymerase chain reaction (PCR) section for amplifying the target nucleic acid sequences in the sample prior to hybridization with the FRET probes.
  • [0081]
    Preferably, the test module also has a microfluidic device mounted in the outer casing adjacent the excitation LED, the microfluidic device having a supporting substrate, CMOS circuitry on the supporting substrate and a microsystems technology (MST) layer on the CMOS circuitry wherein the PCR section and the hybridization chambers are incorporated in the MST layer which has a plurality of channels configured to draw the fluid through the PCR section and into the hybridization chambers by capillary action.
  • [0082]
    Preferably, the test module also has an electrical connection for communication to an external device wherein the CMOS circuitry is configured to convert output from the photodiodes into a signal indicative of the FRET probes that hybridized with the target nucleic acid sequences, and provide the signal to the electrical connection for transmission to the external device.
  • [0083]
    Preferably, the CMOS circuitry has memory for identity data for the different FRET probe types.
  • [0084]
    Preferably, the CMOS circuitry includes the array of photodiodes such that the array of photodiodes is less than 249 microns from the FRET probes.
  • [0085]
    Preferably, the fluorophore has a fluorescence lifetime greater than 100 nanoseconds.
  • [0086]
    Preferably, the FRET probes have a quencher to suppress the fluorescence signal from the fluorophore when the probe is in a non-hybridized configuration, the quencher having no native emission in response to the excitation light.
  • [0087]
    Preferably, the CMOS circuitry is configured for temperature control of the hybridization chambers during hybridization of the probes and the target nucleic acid sequences.
  • [0088]
    The suspended probes with their large excitation and emission optical depth increase the readout sensitivity. The suspended probes are spotted more easily and inexpensively.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • [0089]
    Preferred embodiments of the present invention will now be described by way of example only with reference to the accompanying drawings, in which:
  • [0090]
    FIG. 1 shows a test module and test module reader configured for fluorescence detection;
  • [0091]
    FIG. 2 is a schematic overview of the electronic components in the test module configured for fluorescence detection;
  • [0092]
    FIG. 3 is a schematic overview of the electronic components in the test module reader;
  • [0093]
    FIG. 4 is a schematic representation of the architecture of the LOC device;
  • [0094]
    FIG. 5 is a perspective of the LOC device;
  • [0095]
    FIG. 6 is a plan view of the LOC device with features and structures from all layers superimposed on each other;
  • [0096]
    FIG. 7 is a plan view of the LOC device with the structures of the cap shown in isolation;
  • [0097]
    FIG. 8 is a top perspective of the cap with internal channels and reservoirs shown in dotted line;
  • [0098]
    FIG. 9 is an exploded top perspective of the cap with internal channels and reservoirs shown in dotted line;
  • [0099]
    FIG. 10 is a bottom perspective of the cap showing the configuration of the top channels;
  • [0100]
    FIG. 11 is a plan view of the LOC device showing the structures of the CMOS+MST device in isolation;
  • [0101]
    FIG. 12 is a schematic section view of the LOC device at the sample inlet;
  • [0102]
    FIG. 13 is an enlarged view of Inset AA shown in FIG. 6;
  • [0103]
    FIG. 14 is an enlarged view of Inset AB shown in FIG. 6;
  • [0104]
    FIG. 15 is an enlarged view of Inset AE shown in FIG. 13;
  • [0105]
    FIG. 16 is a partial perspective illustrating the laminar structure of the LOC device within Inset AE;
  • [0106]
    FIG. 17 is a partial perspective illustrating the laminar structure of the LOC device within Inset AE;
  • [0107]
    FIG. 18 is a partial perspective illustrating the laminar structure of the LOC device within Inset AE;
  • [0108]
    FIG. 19 is a partial perspective illustrating the laminar structure of the LOC device within Inset AE;
  • [0109]
    FIG. 20 is a partial perspective illustrating the laminar structure of the LOC device within Inset AE;
  • [0110]
    FIG. 21 is a partial perspective illustrating the laminar structure of the LOC device within Inset AE;
  • [0111]
    FIG. 22 is schematic section view of the lysis reagent reservoir shown in FIG. 21;
  • [0112]
    FIG. 23 is a partial perspective illustrating the laminar structure of the LOC device within Inset AB;
  • [0113]
    FIG. 24 is a partial perspective illustrating the laminar structure of the LOC device within Inset AB;
  • [0114]
    FIG. 25 is a partial perspective illustrating the laminar structure of the LOC device within Inset AI;
  • [0115]
    FIG. 26 is a partial perspective illustrating the laminar structure of the LOC device within Inset AB;
  • [0116]
    FIG. 27 is a partial perspective illustrating the laminar structure of the LOC device within Inset AB;
  • [0117]
    FIG. 28 is a partial perspective illustrating the laminar structure of the LOC device within Inset AB;
  • [0118]
    FIG. 29 is a partial perspective illustrating the laminar structure of the LOC device within Inset AB;
  • [0119]
    FIG. 30 is a schematic section view of the amplification mix reservoir and the polymerase reservoir;
  • [0120]
    FIG. 31 show the features of a boiling-initiated valve in isolation;
  • [0121]
    FIG. 32 is a schematic section view of the boiling-initiated valve taken through line 33-33 shown in FIG. 31;
  • [0122]
    FIG. 33 is an enlarged view of Inset AF shown in FIG. 15;
  • [0123]
    FIG. 34 is a schematic section view of the upstream end of the dialysis section taken through line 35-35 shown in FIG. 33;
  • [0124]
    FIG. 35 is an enlarged view of Inset AC shown in FIG. 6;
  • [0125]
    FIG. 36 is a further enlarged view within Inset AC showing the amplification section;
  • [0126]
    FIG. 37 is a further enlarged view within Inset AC showing the amplification section;
  • [0127]
    FIG. 38 is a further enlarged view within Inset AC showing the amplification section;
  • [0128]
    FIG. 39 is a further enlarged view within Inset AK shown in FIG. 38;
  • [0129]
    FIG. 40 is a further enlarged view within Inset AC showing the amplification chamber;
  • [0130]
    FIG. 41 is a further enlarged view within Inset AC showing the amplification section;
  • [0131]
    FIG. 42 is a further enlarged view within Inset AC showing the amplification chamber;
  • [0132]
    FIG. 43 is a further enlarged view within Inset AL shown in FIG. 42;
  • [0133]
    FIG. 44 is a further enlarged view within Inset AC showing the amplification section;
  • [0134]
    FIG. 45 is a further enlarged view within Inset AM shown in FIG. 44;
  • [0135]
    FIG. 46 is a further enlarged view within Inset AC showing the amplification chamber;
  • [0136]
    FIG. 47 is a further enlarged view within Inset AN shown in FIG. 46;
  • [0137]
    FIG. 48 is a further enlarged view within Inset AC showing the amplification chamber;
  • [0138]
    FIG. 49 is a further enlarged view within Inset AC showing the amplification chamber;
  • [0139]
    FIG. 50 is a further enlarged view within Inset AC showing the amplification section;
  • [0140]
    FIG. 51 is a schematic section view of the amplification section;
  • [0141]
    FIG. 52 is an enlarged plan view of the hybridization section;
  • [0142]
    FIG. 53 is a further enlarged plan view of two hybridization chambers in isolation;
  • [0143]
    FIG. 54 is schematic section view of a single hybridization chamber;
  • [0144]
    FIG. 55 is an enlarged view of the humidifier illustrated in Inset AG shown in FIG. 6;
  • [0145]
    FIG. 56 is an enlarged view of Inset AD shown in FIG. 52;
  • [0146]
    FIG. 57 is an exploded perspective view of the LOC device within Inset AD;
  • [0147]
    FIG. 58 is a diagram of a FRET probe in a closed configuration;
  • [0148]
    FIG. 59 is a diagram of a FRET probe in an open and hybridized configuration;
  • [0149]
    FIG. 60 is a graph of the intensity of an excitation light over time;
  • [0150]
    FIG. 61 is a diagram of the excitation illumination geometry of the hybridization chamber array;
  • [0151]
    FIG. 62 is a diagram of a Sensor Electronic Technology LED illumination geometry;
  • [0152]
    FIG. 63 is an enlarged plan view of the humidity sensor shown in Inset AH of FIG. 6;
  • [0153]
    FIG. 64 is a schematic showing part of the photodiode array of the photo sensor;
  • [0154]
    FIG. 65 is a circuit diagram for a single photodiode;
  • [0155]
    FIG. 66 is a timing diagram for the photodiode control signals;
  • [0156]
    FIG. 67 is an enlarged view of the evaporator shown in Inset AP of FIG. 55;
  • [0157]
    FIG. 68 is a schematic section view through a hybridization chamber with a detection photodiode and trigger photodiode;
  • [0158]
    FIG. 69 is a diagram of linker-primed PCR;
  • [0159]
    FIG. 70 is a schematic representation of a test module with a lancet;
  • [0160]
    FIG. 71 is a diagrammatic representation of the architecture of LOC variant VII;
  • [0161]
    FIG. 72 is a diagrammatic representation of the architecture of LOC variant VIII;
  • [0162]
    FIG. 73 is a schematic illustration of the architecture of LOC variant XIV;
  • [0163]
    FIG. 74 is a schematic illustration of the architecture of LOC variant XLI;
  • [0164]
    FIG. 75 is a schematic illustration of the architecture of LOC variant XLIII;
  • [0165]
    FIG. 76 is a schematic illustration of the architecture of LOC variant XLIV;
  • [0166]
    FIG. 77 is a schematic illustration of the architecture of LOC variant XLVII;
  • [0167]
    FIG. 78 is a diagram of a primer-linked, linear fluorescent probe during the initial round of amplification;
  • [0168]
    FIG. 79 is a diagram of a primer-linked, linear fluorescent probe during a subsequent amplification cycle;
  • [0169]
    FIGS. 80A to 80F diagrammatically illustrate thermal cycling of a primer-linked fluorescent stem-and-loop probe;
  • [0170]
    FIG. 81 is a schematic illustration of the excitation LED relative to the hybridization chamber array and the photodiodes;
  • [0171]
    FIG. 82 is a schematic illustration of the excitation LED and optical lens for directing light onto the hybridization chamber array of the LOC device;
  • [0172]
    FIG. 83 is a schematic illustration of the excitation LED, optical lens, and optical prisms for directing light onto the hybridization chamber array of the LOC device;
  • [0173]
    FIG. 84 is a schematic illustration of the excitation LED, optical lens and mirror arrangement for directing light onto the hybridization chamber array of the LOC device;
  • [0174]
    FIG. 85 is a plan view showing all the features superimposed on each other, and showing the location of Insets DA to DK;
  • [0175]
    FIG. 86 is an enlarged view of Inset DG shown in FIG. 85;
  • [0176]
    FIG. 87 is an enlarged view of Inset DH shown in FIG. 85;
  • [0177]
    FIG. 88 shows one embodiment of the shunt transistor for the photodiodes;
  • [0178]
    FIG. 89 shows one embodiment of the shunt transistor for the photodiodes;
  • [0179]
    FIG. 90 shows one embodiment of the shunt transistor for the photodiodes;
  • [0180]
    FIG. 91 is a circuit diagram of the differential imager;
  • [0181]
    FIG. 92 schematically illustrates a negative control fluorescent probe in its stem-and-loop configuration;
  • [0182]
    FIG. 93 schematically illustrates the negative control fluorescent probe of FIG. 92 in its open configuration;
  • [0183]
    FIG. 94 schematically illustrates a positive control fluorescent probe in its stem-and-loop configuration;
  • [0184]
    FIG. 95 schematically illustrates the positive control fluorescent probe of FIG. 94 in its open configuration;
  • [0185]
    FIG. 96 shows a test module and test module reader configured for use with ECL detection;
  • [0186]
    FIG. 97 is a schematic overview of the electronic components in the test module configured for use with ECL detection;
  • [0187]
    FIG. 98 shows a test module and alternative test module readers;
  • [0188]
    FIG. 99 shows a test module and test module reader along with the hosting system housing various databases;
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Overview
  • [0189]
    This overview identifies the main components of a molecular diagnostic system that incorporates embodiments of the present invention. Comprehensive details of the system architecture and operation are set out later in the specification.
  • [0190]
    Referring to FIGS. 1, 2, 3, 96 and 97, the system has the following top level components:
  • [0191]
    Test modules 10 and 11 are the size of a typical USB memory key and very cheap to produce. Test modules 10 and 11 each contain a microfluidic device, typically in the form of a lab-on-a-chip (LOC) device 30 preloaded with reagents and typically more than 1000 probes for the molecular diagnostic assay (see FIGS. 1 and 96). Test module 10 schematically shown in FIG. 1 uses a fluorescence-based detection technique to identify target molecules, while test module 11 in FIG. 96 uses an electrochemiluminescence-based detection technique. The LOC device 30 has an integrated photosensor 44 for fluorescence or electrochemiluminescence detection (described in detail below). Both test modules 10 and 11 use a standard Micro-USB plug 14 for power, data and control, both have a printed circuit board (PCB) 57, and both have external power supply capacitors 32 and an inductor 15. The test modules 10 and 11 are both single-use only for mass production and distribution in sterile packaging ready for use.
  • [0192]
    The outer casing 13 has a macroreceptacle 24 for receiving the biological sample and a removable sterile sealing tape 22, preferably with a low tack adhesive, to cover the macroreceptacle prior to use. A membrane seal 408 with a membrane guard 410 forms part of the outer casing 13 to reduce dehumidification within the test module while providing pressure relief from small air pressure fluctuations. The membrane guard 410 protects the membrane seal 408 from damage.
  • [0193]
    Test module reader 12 powers the test module 10 or 11 via Micro-USB port 16. The test module reader 12 can adopt many different forms and a selection of these are described later. The version of the reader 12 shown in FIGS. 1, 3 and 96 is a smart phone embodiment. A block diagram of this reader 12 is shown in FIG. 3. Processor 42 runs application software from program storage 43. The processor 42 also interfaces with the display screen 18 and user interface (UI) touch screen 17 and buttons 19, a cellular radio 21, wireless network connection 23, and a satellite navigation system 25. The cellular radio 21 and wireless network connection 23 are used for communications. Satellite navigation system 25 is used for updating epidemiological databases with location data. The location data can, alternatively, be entered manually via the touch screen 17 or buttons 19. Data storage 27 holds genetic and diagnostic information, test results, patient information, assay and probe data for identifying each probe and its array position. Data storage 27 and program storage 43 may be shared in a common memory facility. Application software installed on the test module reader 12 provides analysis of results, along with additional test and diagnostic information.
  • [0194]
    To conduct a diagnostic test, the test module 10 (or test module 11) is inserted into the Micro-USB port 16 on the test module reader 12. The sterile sealing tape 22 is peeled back and the biological sample (in a liquid form) is loaded into the sample macroreceptacle 24. Pressing start button 20 initiates testing via the application software. The sample flows into the LOC device 30 and the on-board assay extracts, incubates, amplifies and hybridizes the sample nucleic acids (the target) with presynthesized hybridization-responsive oligonucleotide probes. In the case of test module 10 (which uses fluorescence-based detection), the probes are fluorescently labelled and the LED 26 housed in the casing 13 provides the necessary excitation light to induce fluorescence emission from the hybridized probes (see FIGS. 1 and 2). In test module 11 (which uses electrochemiluminescence (ECL) detection), the LOC device 30 is loaded with ECL probes (discussed above) and the LED 26 is not necessary for generating the luminescent emission. Instead, electrodes 860 and 870 provide the excitation electrical current (see FIG. 97). The emission (fluorescent or luminescent) is detected using a photosensor 44 integrated into CMOS circuitry of each LOC device. The detected signal is amplified and converted to a digital output which is analyzed by the test module reader 12. The reader then displays the results.
  • [0195]
    The data may be saved locally and/or uploaded to a network server containing patient records. The test module 10 or 11 is removed from the test module reader 12 and disposed of appropriately.
  • [0196]
    FIGS. 1, 3 and 96 show the test module reader 12 configured as a mobile phone/smart phone 28. In other forms, the test module reader is a laptop/notebook 101, a dedicated reader 103, an ebook reader 107, a tablet computer 109 or desktop computer 105 for use in hospitals, private practices or laboratories (see FIG. 98). The reader can interface with a range of additional applications such as patient records, billing, online databases and multi-user environments. It can also be interfaced with a range of local or remote peripherals such as printers and patient smart cards.
  • [0197]
    Referring to FIG. 99, the data generated by the test module 10 can be used to update, via the reader 12 and network 125, the epidemiological databases hosted on the hosting system for epidemiological data 111, the genetic databases hosted on the hosting system for genetic data 113, the electronic health records hosted on the hosting system for electronic health records (EHR) 115, the electronic medical records hosted on the hosting system for electronic medical records (EMR) 121, and the personal health records hosted on the hosting system for personal health records (PHR) 123. Conversely, the epidemiological data hosted on the hosting system for epidemiological data 111, the genetic data hosted on the hosting system for genetic data 113, the electronic health records hosted on the hosting system for electronic health records (EHR) 115, the electronic medical records hosted on the hosting system for electronic medical records (EMR) 121, and the personal health records hosted on the hosting system for personal health records (PHR) 123, can be used to update, via network 125 and the reader 12, the digital memory in the LOC 30 of the test module 10.
  • [0198]
    Referring back to FIGS. 1, 2, 96 and 97 the reader 12 uses battery power in the mobile phone configuration. The mobile phone reader contains all test and diagnostic information preloaded. Data can also be loaded or updated via a number of wireless or contact interfaces to enable communications with peripheral devices, computers or online servers. A Micro-USB port 16 is provided for connection to a computer or mains power supply for battery recharge.
  • [0199]
    FIG. 70 shows an embodiment of the test module 10 used for tests that only require a positive or negative result for a particular target, such as testing whether a person is infected with, for example, H1N1 Influenza A virus. Only a purpose built USB power/indicator-only module 47 is adequate. No other reader or application software is necessary. An indicator 45 on the USB power/indicator-only module 47 signals positive or negative results. This configuration is well suited to mass screening.
  • [0200]
    Additional items supplied with the system may include a test tube containing reagents for pre-treatment of certain samples, along with spatula and lancet for sample collection. FIG. 70 shows an embodiment of the test module incorporating a spring-loaded, retractable lancet 390 and lancet release button 392 for convenience. A satellite phone can be used in remote areas.
  • Test Module Electronics
  • [0201]
    FIGS. 2 and 97 are block diagrams of the electronic components in the test modules 10 and 11, respectively. The CMOS circuitry integrated in the LOC device 30 has a USB device driver 36, a controller 34, a USB-compatible LED driver 29, clock 33, power conditioner 31, RAM 38 and program and data flash memory 40. These provide the control and memory for the entire test module 10 or 11 including the photosensor 44, the temperature sensors 170, the liquid sensors 174, and the various heaters 152, 154, 182, 234, together with associated drivers 37 and 39 and registers 35 and 41. Only the LED 26 (in the case of test module 10), external power supply capacitors 32 and the Micro-USB plug 14 are external to the LOC device 30. The LOC devices 30 include bond-pads for making connections to these external components. The RAM 38 and the program and data flash memory 40 have the application software and the diagnostic and test information (Flash/Secure storage, e.g. via encryption) for over 1000 probes. In the case of test module 11 configured for ECL detection, there is no LED 26 (see FIGS. 96 and 97). Data is encrypted by the LOC device 30 for secure storage and secure communication with an external device. The LOC devices 30 are loaded with electrochemiluminescent probes and the hybridization chambers each have a pair of ECL excitation electrodes 860 and 870.
  • [0202]
    Many types of test modules 10 are manufactured in a number of test forms, ready for off-the-shelf use. The differences between the test forms lie in the on board assay of reagents and probes.
  • [0203]
    Some examples of infectious diseases rapidly identified with this system include:
      • Influenza—Influenza virus A, B, C, Isavirus, Thogotovirus
      • Pneumonia—respiratory syncytial virus (RSV), adenovirus, metapneumovirus, Streptococcus pneumoniae, Staphylococcus aureus
      • Tuberculosis—Mycobacterium tuberculosis, bovis, africanum, canetti, and microti
      • Plasmodium falciparum, Toxoplasma gondii and other protozoan parasites
      • Typhoid—Salmonella enterica serovar typhi
      • Ebola virus
      • Human immunodeficiency virus (HIV)
      • Dengue Fever—Flavivirus
      • Hepatitis (A through E)
      • Hospital acquired infections—for example Clostridium difficile, Vancomycin resistant Enterococcus, and Methicillin resistant Staphylococcus aureus
      • Herpes simplex virus (HSV)
      • Cytomegalovirus (CMV)
      • Epstein-Ban virus (EBV)
      • Encephalitis—Japanese Encephalitis virus, Chandipura virus
      • Whooping cough—Bordetella pertussis
      • Measles—paramyxovirus
      • Meningitis—Streptococcus pneumoniae and Neisseria meningitidis
      • Anthrax—Bacillus anthracis
  • [0222]
    Some examples of genetic disorders identified with this system include:
      • Cystic fibrosis
      • Haemophilia
      • Sickle cell disease
      • Tay-Sachs disease
      • Haemochromatosis
      • Cerebral arteriopathy
      • Crohn's disease
      • Polycistic kidney disease
      • Congential heart disease
      • Rett syndrome
  • [0233]
    A small selection of cancers identified by the diagnostic system include:
      • Ovarian
      • Colon carcinoma
      • Multiple endocrine neoplasia
      • Retinoblastoma
      • Turcot syndrome
  • [0239]
    The above lists are not exhaustive and the diagnostic system can be configured to detect a much greater variety of diseases and conditions using nucleic acid and proteomic analysis.
  • Detailed Architecture of System Components LOC Device
  • [0240]
    The LOC device 30 is central to the diagnostic system. It rapidly performs the four major steps of a nucleic acid based molecular diagnostic assay, i.e. sample preparation, nucleic acid extraction, nucleic acid amplification, and detection, using a microfluidic platform. The LOC device also has alternative uses, and these are detailed later. As discussed above, test modules 10 and 11 can adopt many different configurations to detect different targets Likewise, the LOC device 30 has numerous different embodiments tailored to the target(s) of interest. One form of the LOC device 30 is LOC device 301 for fluorescent detection of target nucleic acid sequences in the pathogens of a whole blood sample. For the purposes of illustration, the structure and operation of LOC device 301 is now described in detail with reference to FIGS. 4 to 26 and 27 to 57.
  • [0241]
    FIG. 4 is a schematic representation of the architecture of the LOC device 301. For convenience, process stages shown in FIG. 4 are indicated with the reference numeral corresponding to the functional sections of the LOC device 301 that perform that process stage. The process stages associated with each of the major steps of a nucleic acid based molecular diagnostic assay are also indicated: sample input and preparation 288, extraction 290, incubation 291, amplification 292 and detection 294. The various reservoirs, chambers, valves and other components of the LOC device 301 will be described in more detail later.
  • [0242]
    FIG. 5 is a perspective view of the LOC device 301. It is fabricated using high volume CMOS and MST (microsystems technology) manufacturing techniques. The laminar structure of the LOC device 301 is illustrated in the schematic (not to scale) partial section view of FIG. 12. The LOC device 301 has a silicon substrate 84 which supports the CMOS+MST chip 48, comprising CMOS circuitry 86 and an MST layer 87, with a cap 46 overlaying the MST layer 87. For the purposes of this patent specification, the term ‘MST layer’ is a reference to a collection of structures and layers that process the sample with various reagents. Accordingly, these structures and components are configured to define flow-paths with characteristic dimensions that will support capillary driven flow of liquids with physical characteristics similar to those of the sample during processing. In light of this, the MST layer and components are typically fabricated using surface micromachining techniques and/or bulk micromachining techniques. However, other fabrication methods can also produce structures and components dimensioned for capillary driven flows and processing very small volumes. The specific embodiments described in this specification show the MST layer as the structures and active components supported on the CMOS circuitry 86, but excluding the features of the cap 46. However, the skilled addressee will appreciate that the MST layer need not have underlying CMOS or indeed an overlying cap in order for it to process the sample.
  • [0243]
    The overall dimensions of the LOC device shown in the following figures are 1760 μm×5824 μm. Of course, LOC devices fabricated for different applications may have different dimensions.
  • [0244]
    FIG. 6 shows the features of the MST layer 87 superimposed with the features of the cap. Insets AA to AD, AG and AH shown in FIG. 6 are enlarged in FIGS. 13, 14, 35, 56, 55 and 63, respectively, and described in detail below for a comprehensive understanding of each structure within the LOC device 301. FIGS. 7 to 10 show the features of the cap 46 in isolation while FIG. 11 shows the CMOS+MST device 48 structures in isolation.
  • Laminar Structure
  • [0245]
    FIGS. 12 and 22 are sketches that diagrammatically show the laminar structure of the CMOS+MST device 48, the cap 46 and the fluidic interaction between the two. The figures are not to scale for the purposes of illustration. FIG. 12 is a schematic section view through the sample inlet 68 and FIG. 22 is a schematic section through the reservoir 54. As best shown in FIG. 12, the CMOS+MST device 48 has a silicon substrate 84 which supports the CMOS circuitry 86 that operates the active elements within the MST layer 87 above. A passivation layer 88 seals and protects the CMOS layer 86 from the fluid flows through the MST layer 87.
  • [0246]
    Fluid flows through both the cap channels 94 and the MST channels 90 (see for example FIGS. 7 and 16) in the cap layer 46 and MST channel layer 100, respectively. Cell transport occurs in the larger channels 94 fabricated in the cap 46, while biochemical processes are carried out in the smaller MST channels 90. Cell transport channels are sized so as to be able to transport cells in the sample to predetermined sites in the MST channels 90. Transportation of cells with sizes greater than 20 microns (for example, certain leukocytes) requires channel dimensions greater than 20 microns, and therefore a cross sectional area transverse to the flow of greater than 400 square microns. MST channels, particularly at locations in the LOC where transport of cells is not required, can be significantly smaller.
  • [0247]
    It will be appreciated that cap channel 94 and MST channel 90 are generic references and particular MST channels 90 may also be referred to as (for example) heated microchannels or dialysis MST channels in light of their particular function. MST channels 90 are formed by etching through a MST channel layer 100 deposited on the passivation layer 88 and patterned with photoresist. The MST channels 90 are enclosed by a roof layer 66 which forms the top (with respect to the orientation shown in the figures) of the CMOS+MST device 48.
  • [0248]
    Despite sometimes being shown as separate layers, the cap channel layer 80 and the reservoir layer 78 are formed from a unitary piece of material. Of course, the piece of material may also be non-unitary. This piece of material is etched from both sides in order to form a cap channel layer 80 in which the cap channels 94 are etched and the reservoir layer 78 in which the reservoirs 54, 56, 58, 60 and 62 are etched. Alternatively, the reservoirs and the cap channels are formed by a micromolding process. Both etching and micromolding techniques are used to produce channels with cross sectional areas transverse to the flow as large as 20,000 square microns, and as small as 8 square microns.
  • [0249]
    At different locations in the LOC device, there can be a range of appropriate choices for the cross sectional area of the channel transverse to the flow. Where large quantities of sample, or samples with large constituents, are contained in the channel, a cross-sectional area of up to 20,000 square microns (for example, a 200 micron wide channel in a 100 micron thick layer) is suitable. Where small quantities of liquid, or mixtures without large cells present, are contained in the channel, a very small cross sectional area transverse to the flow is preferable.
  • [0250]
    A lower seal 64 encloses the cap channels 94 and the upper seal layer 82 encloses the reservoirs 54, 56, 58, 60 and 62.
  • [0251]
    The five reservoirs 54, 56, 58, 60 and 62 are preloaded with assay-specific reagents. In the embodiment described here, the reservoirs are preloaded with the following reagents, but other reagents can easily be substituted:
      • reservoir 54: anticoagulant with option to include erythrocyte lysis buffer
      • reservoir 56: lysis reagent
      • reservoir 58: restriction enzymes, ligase and linkers (for linker-primed PCR (see FIG. 69, extracted from T. Stachan et al., Human Molecular Genetics 2, Garland Science, NY and London, 1999))
      • reservoir 60: amplification mix (dNTPs, primers, buffer) and
      • reservoir 62: DNA polymerase.
  • [0257]
    The cap 46 and the CMOS+MST layers 48 are in fluid communication via corresponding openings in the lower seal 64 and the roof layer 66. These openings are referred to as uptakes 96 and downtakes 92 depending on whether fluid is flowing from the MST channels 90 to the cap channels 94 or vice versa.
  • LOC Device Operation
  • [0258]
    The operation of the LOC device 301 is described below in a step-wise fashion with reference to analysing pathogenic DNA in a blood sample. Of course, other types of biological or non-biological fluid are also analysed using an appropriate set, or combination, of reagents, test protocols, LOC variants and detection systems. Referring back to FIG. 4, there are five major steps involved in analysing a biological sample, comprising sample input and preparation 288, nucleic acid extraction 290, nucleic acid incubation 291, nucleic acid amplification 292 and detection and analysis 294.
  • [0259]
    The sample input and preparation step 288 involves mixing the blood with an anticoagulant 116 and then separating pathogens from the leukocytes and erythrocytes with the pathogen dialysis section 70. As best shown in FIGS. 7 and 12, the blood sample enters the device via the sample inlet 68. Capillary action draws the blood sample along the cap channel 94 to the reservoir 54. Anticoagulant is released from the reservoir 54 as the sample blood flow opens its surface tension valve 118 (see FIGS. 15 and 22). The anticoagulant prevents the formation of clots which would block the flow.
  • [0260]
    As best shown in FIG. 22, the anticoagulant 116 is drawn out of the reservoir 54 by capillary action and into the MST channel 90 via the downtake 92. The downtake 92 has a capillary initiation feature (CIF) 102 to shape the geometry of the meniscus such that it does not anchor to the rim of the downtake 92. Vent holes 122 in the upper seal 82 allows air to replace the anticoagulant 116 as it is drawn out of the reservoir 54.
  • [0261]
    The MST channel 90 shown in FIG. 22 is part of a surface tension valve 118. The anticoagulant 116 fills the surface tension valve 118 and pins a meniscus 120 to the uptake 96 to a meniscus anchor 98. Prior to use, the meniscus 120 remains pinned at the uptake 96 so the anticoagulant does not flow into the cap channel 94. When the blood flows through the cap channel 94 to the uptake 96, the meniscus 120 is removed and the anticoagulant is drawn into the flow.
  • [0262]
    FIGS. 15 to 21 show Inset AE which is a portion of Inset AA shown in FIG. 13. As shown in FIGS. 15, 16 and 17, the surface tension valve 118 has three separate MST channels 90 extending between respective downtakes 92 and uptakes 96. The number of MST channels 90 in a surface tension valve can be varied to change the flow rate of the reagent into the sample mixture. As the sample mixture and the reagents mix together by diffusion, the flow rate out of the reservoir determines the concentration of the reagent in the sample flow. Hence, the surface tension valve for each of the reservoirs is configured to match the desired reagent concentration.
  • [0263]
    The blood passes into a pathogen dialysis section 70 (see FIGS. 4 and 15) where target cells are concentrated from the sample using an array of apertures 164 sized according to a predetermined threshold. Cells smaller than the threshold pass through the apertures while larger cells do not pass through the apertures. Unwanted cells, which may be either the larger cells withheld by the array of apertures 164 or the smaller cells that pass through the apertures, are redirected to a waste unit 76 while the target cells continue as part of the assay.
  • [0264]
    In the pathogen dialysis section 70 described here, the pathogens from the whole blood sample are concentrated for microbial DNA analysis. The array of apertures is formed by a multitude of 3 micron diameter holes 164 fluidically connecting the input flow in the cap channel 94 to a target channel 74. The 3 micron diameter apertures 164 and the dialysis uptake holes 168 for the target channel 74 are connected by a series of dialysis MST channels 204 (best shown in FIGS. 15 and 21). Pathogens are small enough to pass through the 3 micron diameter apertures 164 and fill the target channel 74 via the dialysis MST channels 204. Cells larger than 3 microns, such as erythrocytes and leukocytes, stay in the waste channel 72 in the cap 46 which leads to a waste reservoir 76 (see FIG. 7).
  • [0265]
    Other aperture shapes, sizes and aspect ratios can be used to isolate specific pathogens or other target cells such as leukocytes for human DNA analysis. Greater detail on the dialysis section and dialysis variants is provided later.
  • [0266]
    Referring again to FIGS. 6 and 7, the flow is drawn through the target channel 74 to the surface tension valve 128 of the lysis reagent reservoir 56. The surface tension valve 128 has seven MST channels 90 extending between the lysis reagent reservoir 56 and the target channel 74. When the menisci are unpinned by the sample flow, the flow rate from all seven of the MST channels 90 will be greater than the flow rate from the anticoagulant reservoir 54 where the surface tension valve 118 has three MST channels 90 (assuming the physical characteristics of the fluids are roughly equivalent). Hence the proportion of lysis reagent in the sample mixture is greater than that of the anticoagulant.
  • [0267]
    The lysis reagent and target cells mix by diffusion in the target channel 74 within the chemical lysis section 130. A boiling-initiated valve 126 stops the flow until sufficient time has passed for diffusion and lysis to take place, releasing the genetic material from the target cells (see FIGS. 6 and 7). The structure and operation of the boiling-initiated valves are described in greater detail below with reference to FIGS. 31 and 32. Other active valve types (as opposed to passive valves such as the surface tension valve 118) have also been developed by the Applicant which may be used here instead of the boiling-initiated valve. These alternative valve designs are also described later.
  • [0268]
    When the boiling-initiated valve 126 opens, the lysed cells flow into a mixing section 131 for pre-amplification restriction digestion and linker ligation.
  • [0269]
    Referring to FIG. 13, restriction enzymes, linkers and ligase are released from the reservoir 58 when the flow unpins the menisci at the surface tension valve 132 at the start of the mixing section 131. The mixture flows the length of the mixing section 131 for diffusion mixing. At the end of the mixing section 131 is downtake 134 leading into the incubator inlet channel 133 of the incubation section 114 (see FIG. 13). The incubator inlet channel 133 feeds the mixture into a serpentine configuration of heated microchannels 210 which provides an incubation chamber for holding the sample during restriction digestion and ligation of the linkers (see FIGS. 13 and 14).
  • [0270]
    FIGS. 23, 24, 25, 26, 27, 28 and 29 show the layers of the LOC device 301 within Inset AB of FIG. 6. Each figure shows the sequential addition of layers forming the structures of the CMOS+MST layer 48 and the cap 46. Inset AB shows the end of the incubation section 114 and the start of the amplification section 112. As best shown in FIGS. 14 and 23, the flow fills the microchannels 210 of the incubation section 114 until reaching the boiling-initiated valve 106 where the flow stops while diffusion takes place. As discussed above, the microchannel 210 upstream of the boiling-initiated valve 106 becomes an incubation chamber containing the sample, restriction enzymes, ligase and linkers. The heaters 154 are then activated and held at constant temperature for a specified time for restriction digestion and linker ligation to occur.
  • [0271]
    The skilled worker will appreciate that this incubation step 291 (see FIG. 4) is optional and only required for some nucleic acid amplification assay types. Furthermore, in some instances, it may be necessary to have a heating step at the end of the incubation period to spike the temperature above the incubation temperature. The temperature spike inactivates the restriction enzymes and ligase prior to entering the amplification section 112. Inactivation of the restriction enzymes and ligase has particular relevance when isothermal nucleic acid amplification is being employed.
  • [0272]
    Following incubation, the boiling-initiated valve 106 is activated (opened) and the flow resumes into the amplification section 112. Referring to FIGS. 31 and 32, the mixture fills the serpentine configuration of heated microchannels 158, which form one or more amplification chambers, until it reaches the boiling-initiated valve 108. As best shown in the schematic section view of FIG. 30, amplification mix (dNTPs, primers, buffer) is released from reservoir 60 and polymerase is subsequently released from reservoir 62 into the intermediate MST channel 212 connecting the incubation and amplification sections (114 and 112 respectively).
  • [0273]
    FIGS. 35 to 51 show the layers of the LOC device 301 within Inset AC of FIG. 6. Each figure shows the sequential addition of layers forming the structures of the CMOS+MST device 48 and the cap 46. Inset AC is at the end of the amplification section 112 and the start of the hybridization and detection section 52. The incubated sample, amplification mix and polymerase flow through the microchannels 158 to the boiling-initiated valve 108. After sufficient time for diffusion mixing, the heaters 154 in the microchannels 158 are activated for thermal cycling or isothermal amplification. The amplification mix goes through a predetermined number of thermal cycles or a preset amplification time to amplify sufficient target DNA. After the nucleic acid amplification process, the boiling-initiated valve 108 opens and flow resumes into the hybridization and detection section 52. The operation of boiling-initiated valves is described in more detail later.
  • [0274]
    As shown in FIG. 52, the hybridization and detection section 52 has an array of hybridization chambers 110. FIGS. 52, 53, 54 and 56 show the hybridization chamber array 110 and individual hybridization chambers 180 in detail. At the entrance to the hybridization chamber 180 is a diffusion barrier 175 which prevents diffusion of the target nucleic acid, probe strands and hybridized probes between the hybridization chambers 180 during hybridization so as to prevent erroneous hybridization detection results. The diffusion barriers 175 present a flow-path-length that is long enough to prevent the target sequences and probes diffusing out of one chamber and contaminating another chamber within the time taken for the probes and nucleic acids to hybridize and the signal to be detected, thus avoiding an erroneous result.
  • [0275]
    Another mechanism to prevent erroneous readings is to have identical probes in a number of the hybridization chambers. The CMOS circuitry 86 derives a single result from the photodiodes 184 corresponding to the hybridization chambers 180 that contain identical probes. Anomalous results can be disregarded or weighted differently in the derivation of the single result.
  • [0276]
    The thermal energy required for hybridization is provided by CMOS-controlled heaters 182 (described in more detail below). After the heater is activated, hybridization occurs between complementary target-probe sequences. The LED driver 29 in the CMOS circuitry 86 signals the LED 26 located in the test module 10 to illuminate. These probes only fluoresce when hybridization has occurred thereby avoiding washing and drying steps that are typically required to remove unbound strands. Hybridization forces the stem-and-loop structure of the FRET probes 186 to open, which allows the fluorophore to emit fluorescent energy in response to the LED excitation light, as discussed in greater detail later. Fluorescence is detected by a photodiode 184 in the CMOS circuitry 86 underlying each hybridization chamber 180 (see hybridization chamber description below). The photodiodes 184 for all hybridization chambers and associated electronics collectively form the photosensor 44 (see FIG. 64). In other embodiments, the photosensor may be an array of charge coupled devices (CCD array). The detected signal from the photodiodes 184 is amplified and converted to a digital output which is analyzed by the test module reader 12. Further details of the detection method are described later.
  • Additional Details for the LOC Device Modularity of the Design
  • [0277]
    The LOC device 301 has many functional sections, including the reagent reservoirs 54, 56, 58, 60 and 62, the dialysis section 70, lysis section 130, incubation section 114, and amplification section 112, valve types, the humidifier and humidity sensor. In other embodiments of the LOC device, these functional sections can be omitted, additional functional sections can be added or the functional sections can be used for alternative purposes to those described above.
  • [0278]
    For example, the incubation section 114 can be used as the first amplification section 112 of a tandem amplification assay system, with the chemical lysis reagent reservoir 56 being used to add the first amplification mix of primers, dNTPs and buffer and reagent reservoir 58 being used for adding the reverse transcriptase and/or polymerase. A chemical lysis reagent can also be added to the reservoir 56 along with the amplification mix if chemical lysis of the sample is desired or, alternatively, thermal lysis can occur in the incubation section by heating the sample for a predetermined time. In some embodiments, an additional reservoir can be incorporated immediately upstream of reservoir 58 for the mix of primers, dNTPs and buffer if there is a requirement for chemical lysis and a separation of this mix from the chemical lysis reagent is desired.
  • [0279]
    In some circumstances it may be desirable to omit a step, such as the incubation step 291. In this case, a LOC device can be specifically fabricated to omit the reagent reservoir 58 and incubation section 114, or the reservoir can simply not be loaded with reagents or the active valves, if present, not activated to dispense the reagents into the sample flow, and the incubation section then simply becomes a channel to transport the sample from the lysis section 130 to the amplification section 112. The heaters are independently operable and therefore, where reactions are dependent on heat, such as thermal lysis, programming the heaters not to activate during this step ensures thermal lysis does not occur in LOC devices that do not require it. The dialysis section 70 can be located at the beginning of the fluidic system within the microfluidic device as shown in FIG. 4 or can be located anywhere else within the microfluidic device. For example, dialysis after the amplification phase 292 to remove cellular debris prior to the hybridization and detection step 294 may be beneficial in some circumstances. Alternatively, two or more dialysis sections can be incorporated at any location throughout the LOC device. Similarly, it is possible to incorporate additional amplification sections 112 to enable multiple targets to be amplified in parallel or in series prior to being detected in the hybridization chamber arrays 110 with specific nucleic acid probes. For analysis of samples like whole blood, in which dialysis is not required, the dialysis section 70 is simply omitted from the sample input and preparation section 288 of the LOC design. In some cases, it is not necessary to omit the dialysis section 70 from the LOC device even if the analysis does not require dialysis. If there is no geometric hindrance to the assay by the existence of a dialysis section, a LOC with the dialysis section 70 in the sample input and preparation section can still be used without a loss of the required functionality.
  • [0280]
    Furthermore, the detection section 294 may encompass proteomic chamber arrays which are identical to the hybridization chamber arrays but are loaded with probes designed to conjugate or hybridize with sample target proteins present in non-amplified sample instead of nucleic acid probes designed to hybridize to target nucleic acid sequences.
  • [0281]
    It will be appreciated that the LOC devices fabricated for use in this diagnostic system are different combinations of functional sections selected in accordance with the particular LOC application. The vast majority of functional sections are common to many of the LOC devices and the design of additional LOC devices for new application is a matter of compiling an appropriate combination of functional sections from the extensive selection of functional sections used in the existing LOC devices.
  • [0282]
    Only a small number of the LOC devices are shown in this description and some more are shown schematically to illustrate the design flexibility of the LOC devices fabricated for this system. The person skilled in the art will readily recognise that the LOC devices shown in this description are not an exhaustive list and many additional LOC designs are a matter of compiling the appropriate combination of functional sections.
  • Sample Types
  • [0283]
    LOC variants can accept and analyze the nucleic acid or protein content of a variety of sample types in liquid form including, but not limited to, blood and blood products, saliva, cerebrospinal fluid, urine, semen, amniotic fluid, umbilical cord blood, breast milk, sweat, pleural effusion, tear, pericardial fluid, peritoneal fluid, environmental water samples and drink samples. Amplicon obtained from macroscopic nucleic acid amplification can also be analysed using the LOC device; in this case, all the reagent reservoirs will be empty or configured not to release their contents, and the dialysis, lysis, incubation and amplification sections will be used solely to transport the sample from the sample inlet 68 to the hybridization chambers 180 for nucleic acid detection, as described above.
  • [0284]
    For some sample types, a pre-processing step is required, for example semen may need to be liquefied and mucus may need to be pre-treated with an enzyme to reduce the viscosity prior to input into the LOC device.
  • Sample Input
  • [0285]
    Referring to FIGS. 1 and 12, the sample is added to the macroreceptacle 24 of the test module 10. The macroreceptacle 24 is a truncated cone which feeds into the inlet 68 of the LOC device 301 by capillary action. Here it flows into the 64 μm wide×60 μm deep cap channel 94 where it is drawn towards the anticoagulant reservoir 54, also by capillary action.
  • Reagent Reservoirs
  • [0286]
    The small volumes of reagents required by the assay systems using microfluidic devices, such as LOC device 301, permit the reagent reservoirs to contain all reagents necessary for the biochemical processing with each of the reagent reservoirs having a small volume. This volume is easily less than 1,000,000,000 cubic microns, in the vast majority of cases less than 300,000,000 cubic microns, typically less than 70,000,000 cubic microns and in the case of the LOC device 301 shown in the drawings, less than 20,000,000 cubic microns.
  • Dialysis Section
  • [0287]
    Referring to FIGS. 15 to 21, 33 and 34, the pathogen dialysis section 70 is designed to concentrate pathogenic target cells from the sample. As previously described, a plurality of apertures in the form of 3 micron diameter holes 164 in the roof layer 66 filter the target cells from the bulk of the sample. As the sample flows past the 3 micron diameter apertures 164, microbial pathogens pass through the holes into a series of dialysis MST channels 204 and flow back up into the target channel 74 via 16 μm dialysis uptake holes 168 (see FIGS. 33 and 34). The remainder of the sample (erythrocytes and so on) stay in the cap channel 94. Downstream of the pathogen dialysis section 70, the cap channel 94 becomes the waste channel 72 leading to the waste reservoir 76. For biological samples of the type that generate a substantial amount of waste, a foam insert or other porous element 49 within the outer casing 13 of the test module 10 is configured to be in fluid communication with the waste reservoir 76 (see FIG. 1).
  • [0288]
    The pathogen dialysis section 70 functions entirely on capillary action of the fluid sample. The 3 micron diameter apertures 164 at the upstream end of the pathogen dialysis section 70 have capillary initiation features (CIFs) 166 (see FIG. 33) so that the fluid is drawn down into the dialysis MST channel 204 beneath. The first uptake hole 198 for the target channel 74 also has a CIF 202 (see FIG. 15) to avoid the flow simply pinning a meniscus across the dialysis uptake holes 168.
  • [0289]
    The small constituents dialysis section 682 schematically shown in FIG. 74 can have a similar structure to the pathogen dialysis section 70. The small constituents dialysis section separates any small target cells or molecules from a sample by sizing (and, if necessary, shaping) apertures suitable for allowing the small target cells or molecules to pass into the target channel and continue for further analysis. Larger sized cells or molecules are removed to a waste reservoir 766. Thus, the LOC device 30 (see FIGS. 1 and 96) is not limited to separating pathogens that are less than 3 μm in size, but can be used to separate cells or molecules of any size desired.
  • Lysis Section
  • [0290]
    Referring back to FIGS. 7, 11 and 13, the genetic material in the sample is released from the cells by a chemical lysis process. As described above, a lysis reagent from the lysis reservoir 56 mixes with the sample flow in the target channel 74 downstream of the surface tension valve 128 for the lysis reservoir 56. However, some diagnostic assays are better suited to a thermal lysis process, or even a combination of chemical and thermal lysis of the target cells. The LOC device 301 accommodates this with the heated microchannels 210 of the incubation section 114. The sample flow fills the incubation section 114 and stops at the boiling-initiated valve 106. The incubation microchannels 210 heat the sample to a temperature at which the cellular membranes are disrupted.
  • [0291]
    In some thermal lysis applications, an enzymatic reaction in the chemical lysis section 130 is not necessary and the thermal lysis completely replaces the enzymatic reaction in the chemical lysis section 130.
  • Boiling-Initiated Valve
  • [0292]
    As discussed above, the LOC device 301 has three boiling-initiated valves 126, 106 and 108. The location of these valves is shown in FIG. 6. FIG. 31 is an enlarged plan view of the boiling-initiated valve 108 in isolation at the end of the heated microchannels 158 of the amplification section 112.
  • [0293]
    The sample flow 119 is drawn along the heated microchannels 158 by capillary action until it reaches the boiling-initiated valve 108. The leading meniscus 120 of the sample flow pins at a meniscus anchor 98 at the valve inlet 146. The geometry of the meniscus anchor 98 stops the advancing meniscus to arrest the capillary flow. As shown in FIGS. 31 and 32, the meniscus anchor 98 is an aperture provided by an uptake opening from the MST channel 90 to the cap channel 94. Surface tension in the meniscus 120 keeps the valve closed. An annular heater 152 is at the periphery of the valve inlet 146. The annular heater 152 is CMOS-controlled via the boiling-initiated valve heater contacts 153.
  • [0294]
    To open the valve, the CMOS circuitry 86 sends an electrical pulse to the valve heater contacts 153. The annular heater 152 resistively heats until the liquid sample 119 boils. The boiling unpins the meniscus 120 from the valve inlet 146 and initiates wetting of the cap channel 94. Once wetting the cap channel 94 begins, capillary flow resumes. The fluid sample 119 fills the cap channel 94 and flows through the valve downtake 150 to the valve outlet 148 where capillary driven flow continues along the amplification section exit channel 160 into the hybridization and detection section 52. Liquid sensors 174 are placed before and after the valve for diagnostics.
  • [0295]
    It will be appreciated that once the boiling-initiated valves are opened, they cannot be re-closed. However, as the LOC device 301 and the test module 10 are single-use devices, re-closing the valves is unnecessary.
  • Incubation Section and Nucleic Acid Amplification Section
  • [0296]
    FIGS. 6, 7, 13, 14, 23, 24, 25, 35 to 45, 50 and 51 show the incubation section 114 and the amplification section 112. The incubation section 114 has a single, heated incubation microchannel 210 etched in a serpentine pattern in the MST channel layer 100 from the downtake opening 134 to the boiling-initiated valve 106 (see FIGS. 13 and 14). Control over the temperature of the incubation section 114 enables enzymatic reactions to take place with greater efficiency. Similarly, the amplification section 112 has a heated amplification microchannel 158 in a serpentine configuration leading from the boiling-initiated valve 106 to the boiling-initiated valve 108 (see FIGS. 6 and 14). These valves arrest the flow to retain the target cells in the heated incubation or amplification microchannels 210 or 158 while mixing, incubation and nucleic acid amplification takes place. The serpentine pattern of the microchannels also facilitates (to some extent) mixing of the target cells with reagents.
  • [0297]
    In the incubation section 114 and the amplification section 112, the sample cells and the reagents are heated by the heaters 154 controlled by the CMOS circuitry 86 using pulse width modulation (PWM). Each meander of the serpentine configuration of the heated incubation microchannel 210 and amplification microchannel 158 has three separately operable heaters 154 extending between their respective heater contacts 156 (see FIG. 14) which provides for the two-dimensional control of input heat flux density. As best shown in FIG. 51, the heaters 154 are supported on the roof layer 66 and embedded in the lower seal 64. The heater material is TiAl but many other conductive metals would be suitable. The elongate heaters 154 are parallel with the longitudinal extent of each channel section that forms the wide meanders of the serpentine shape. In the amplification section 112, each of the wide meanders can operate as separate PCR chambers via individual heater control.
  • [0298]
    The small volumes of amplicon required by the assay systems using microfluidic devices, such as LOC device 301, permit low amplification mixture volumes for amplification in amplification section 112. This volume is easily less than 400 nanoliters, in the vast majority of cases less than 170 nanoliters, typically less than 70 nanoliters and in the case of the LOC device 301, between 2 nanoliters and 30 nanoliters.
  • Increased Rates of Heating and Greater Diffusive Mixing
  • [0299]
    The small cross section of each channel section increases the heating rate of the amplification fluid mix. All the fluid is kept a relatively short distance from the heater 154. Reducing the channel cross section (that is the amplification microchannel 158 cross section) to less than 100,000 square microns achieves appreciably higher heating rates than that provided by more ‘macro-scale’ equipment. Lithographic fabrication techniques allow the amplification microchannel 158 to have a cross sectional area transverse to the flow-path less than 16,000 square microns which gives substantially higher heating rates. Feature sizes on the order of 1 micron are readily achievable with lithographic techniques. If very little amplicon is needed (as is the case in the LOC device 301), the cross sectional area can be reduced to less than 2,500 square microns. For diagnostic assays with 1,000 to 2,000 probes on the LOC device, and a requirement of ‘sample-in, answer out’ in less than 1 minute, a cross sectional area transverse to the flow of between 400 square microns and 1 square micron is adequate.
  • [0300]
    The heater element in the amplification microchannel 158 heats the nucleic acid sequences at a rate more than 80 Kelvin (K) per second, in the vast majority of cases at a rate greater than 100 K per second. Typically, the heater element heats the nucleic acid sequences at a rate more than 1,000 K per second and in many cases, the heater element heats the nucleic acid sequences at a rate more than 10,000 K per second. Commonly, based on the demands of the assay system, the heater element heats the nucleic acid sequences at a rate more than 100,000 K per second, more than 1,000,000 K per second more than 10,000,000 K per second, more than 20,000,000 K per second, more than 40,000,000 K per second, more than 80,000,000 K per second and more than 160,000,000 K per second.
  • [0301]
    A small cross-sectional area channel is also beneficial for diffusive mixing of any reagents with the sample fluid. Before diffusive mixing is complete, diffusion of one liquid into the other is greatest near the interface between the two. Concentration decreases with distance from the interface. Using microchannels with relatively small cross sections transverse to the flow direction, keeps both fluid flows close to the interface for more rapid diffusive mixing. Reducing the channel cross section to less than 100,000 square microns achieves appreciably higher mixing rates than that provided by more ‘macro-scale’ equipment. Lithographic fabrication techniques allows microchannels with a cross sectional area transverse to the flow-path less than 16000 square microns which gives significantly higher mixing rates. If small volumes are needed (as is the case in the LOC device 301), the cross sectional area can be reduced to less than 2500 square microns. For diagnostic assays with 1000 to 2000 probes on the LOC device, and a requirement of ‘sample-in, answer out’ in less than 1 minute, a cross sectional area transverse to the flow of between 400 square microns and 1 square micron is adequate.
  • Short Thermal Cycle Times
  • [0302]
    Keeping the sample mixture proximate to the heaters, and using very small fluid volumes allows rapid thermal cycling during the nucleic acid amplification process. Each thermal cycle (i.e. denaturing, annealing and primer extension) is completed in less than 30 seconds for target sequences up to 150 base pairs (bp) long. In the vast majority of diagnostic assays, the individual thermal cycle times are less than 11 seconds, and a large proportion are less than 4 seconds. LOC devices 30 with some of the most common diagnostic assays have thermal cycles time between 0.45 seconds to 1.5 seconds for target sequences up to 150 bp long. Thermal cycling at this rate allows the test module to complete the nucleic acid amplification process in much less than 10 minutes; often less than 220 seconds. For most assays, the amplification section generates sufficient amplicon in less than 80 seconds from the sample fluid entering the sample inlet. For a great many assays, sufficient amplicon is generated in 30 seconds.
  • [0303]
    Upon completion of a preset number of amplification cycles, the amplicon is fed into the hybridization and detection section 52 via the boiling-initiated valve 108.
  • Hybridization Chambers
  • [0304]
    FIGS. 52, 53, 54, 56 and 57 show the hybridization chambers 180 in the hybridization chamber array 110. The hybridization and detection section 52 has a 24×45 array 110 of hybridization chambers 180, each with hybridization-responsive FRET probes 186, heater element 182 and an integrated photodiode 184. The photodiode 184 is incorporated for detection of fluorescence resulting from the hybridization of a target nucleic acid sequence or protein with the FRET probes 186. Each photodiode 184 is independently controlled by the CMOS circuitry 86. Any material between the FRET probes 186 and the photodiode 184 must be transparent to the emitted light. Accordingly, the wall section 97 between the probes 186 and the photodiode 184 is also optically transparent to the emitted light. In the LOC device 301, the wall section 97 is a thin (approximately 0.5 micron) layer of silicon dioxide.
  • [0305]
    Incorporation of a photodiode 184 directly beneath each hybridization chamber 180 allows the volume of probe-target hybrids to be very small while still generating a detectable fluorescence signal (see FIG. 54). The small amounts permit small volume hybridization chambers. A detectable amount of probe-target hybrid requires a quantity of probe, prior to hybridization, which is easily less than 270 picograms (corresponding to 900,000 cubic microns), in the vast majority of cases less than 60 picograms (corresponding to 200,000 cubic microns), typically less than 12 picograms (corresponding to 40,000 cubic microns) and in the case of the LOC device 301 shown in the accompanying figures, less than 2.7 picograms (corresponding to a chamber volume of 9,000 cubic microns). Of course, reducing the size of the hybridization chambers allows a higher density of chambers and therefore more probes on the LOC device. In LOC device 301, the hybridization section has more than 1,000 chambers in an area of 1,500 microns by 1,500 microns (i.e. less than 2,250 square microns per chamber). Smaller volumes also reduce the reaction times so that hybridization and detection is faster. An additional advantage of the small amount of probe required in each chamber is that only very small quantities of probe solution need to be spotted into each chamber during production of the LOC device. Embodiments of the LOC device according to the invention can be spotted using a probe solution volume of 1 picoliter or less.
  • [0306]
    After nucleic acid amplification, boiling-initiated valve 108 is activated and the amplicon flows along the flow-path 176 and into each of the hybridization chambers 180 (see FIGS. 52 and 56). An end-point liquid sensor 178 indicates when the hybridization chambers 180 are filled with amplicon and the heaters 182 can be activated.
  • [0307]
    After sufficient hybridization time, the LED 26 (see FIG. 2) is activated. The opening in each of the hybridization chambers 180 provides an optical window 136 for exposing the FRET probes 186 to the excitation radiation (see FIGS. 52, 54 and 56). The LED 26 is illuminated for a sufficiently long time in order to induce a fluorescence signal from the probes with high intensity. During excitation, the photodiode 184 is shorted. After a pre-programmed delay 300 (see FIG. 2), the photodiode 184 is enabled and fluorescence emission is detected in the absence of the excitation light. The incident light on the active area 185 of the photodiode 184 (see FIG. 54) is converted into a photocurrent which can then be measured using CMOS circuitry 86.
  • [0308]
    The hybridization chambers 180 are each loaded with probes for detecting a single target nucleic acid sequence. Each hybridization chambers 180 can be loaded with probes to detect over 1,000 different targets if desired. Alternatively, many or all the hybridization chambers can be loaded with the same probes to detect the same target nucleic acid repeatedly. Replicating the probes in this way throughout the hybridization chamber array 110 leads to increased confidence in the results obtained and the results can be combined by the photodiodes adjacent those hybridization chambers to provide a single result if desired. The person skilled in the art will recognise that it is possible to have from one to over 1,000 different probes on the hybridization chamber array 110, depending on the assay specification.
  • Humidifier and Humidity Sensor
  • [0309]
    Inset AG of FIG. 6 indicates the position of the humidifier 196. The humidifier prevents evaporation of the reagents and probes during operation of the LOC device 301. As best shown in the enlarged view of FIG. 55, a water reservoir 188 is fluidically connected to three evaporators 190. The water reservoir 188 is filled with molecular biology-grade water and sealed during manufacturing. As best shown in FIGS. 55 and 67, water is drawn into three downtakes 194 and along respective water supply channels 192 by capillary action to a set of three uptakes 193 at the evaporators 190. A meniscus pins at each uptake 193 to retain the water. The evaporators have annular shaped heaters 191 which encircle the uptakes 193. The annular heaters 191 are connected to the CMOS circuitry 86 by the conductive columns 376 to the top metal layer 195 (see FIG. 37). Upon activation, the annular heaters 191 heat the water causing evaporation and humidifying the device surrounds.
  • [0310]
    The position of the humidity sensor 232 is also shown in FIG. 6. However, as best shown in the enlarged view of Inset AH in FIG. 63, the humidity sensor has a capacitive comb structure. A lithographically etched first electrode 296 and a lithographically etched second electrode 298 face each other such that their teeth are interleaved. The opposed electrodes form a capacitor with a capacitance that can be monitored by the CMOS circuitry 86. As the humidity increases, the permittivity of the air gap between the electrodes increases, so that the capacitance also increases. The humidity sensor 232 is adjacent the hybridization chamber array 110 where humidity measurement is most important to slow evaporation from the solution containing the exposed probes.
  • Feedback Sensors
  • [0311]
    Temperature and liquid sensors are incorporated throughout the LOC device 301 to provide feedback and diagnostics during device operation. Referring to FIG. 35, nine temperature sensors 170 are distributed throughout the amplification section 112. Likewise, the incubation section 114 also has nine temperature sensors 170. These sensors each use a 2×2 array of bipolar junction transistors (BJTs) to monitor the fluid temperature and provide feedback to the CMOS circuitry 86. The CMOS circuitry 86 uses this to precisely control the thermal cycling during the nucleic acid amplification process and any heating during thermal lysis and incubation.
  • [0312]
    In the hybridization chambers 180, the CMOS circuitry 86 uses the hybridization heaters 182 as temperature sensors (see FIG. 56). The electrical resistance of the hybridization heaters 182 is temperature dependent and the CMOS circuitry 86 uses this to derive a temperature reading for each of the hybridization chambers 180.
  • [0313]
    The LOC device 301 also has a number of MST channel liquid sensors 174 and cap channel liquid sensors 208. FIG. 35 shows a line of MST channel liquid sensors 174 at one end of every other meander in the heated microchannel 158. As best shown in FIG. 37, the MST channel liquid sensors 174 are a pair of electrodes formed by exposed areas of the top metal layer 195 in the CMOS structure 86. Liquid closes the circuit between the electrodes to indicate its presence at the sensor's location.
  • [0314]
    FIG. 25 shows an enlarged perspective of cap channel liquid sensors 208. Opposing pairs of TiAl electrodes 218 and 220 are deposited on the roof layer 66. Between the electrodes 218 and 220 is a gap 222 to hold the circuit open in the absence of liquid. The presence of liquid closes the circuit and the CMOS circuitry 86 uses this feedback to monitor the flow.
  • Gravitational Independence
  • [0315]
    The test modules 10 are orientation independent. They do not need to be secured to a flat stable surface in order to operate. Capillary driven fluid flows and a lack of external plumbing into ancillary equipment allow the modules to be truly portable and simply plugged into a similarly portable hand held reader such as a mobile telephone. Having a gravitationally independent operation means the test modules are also accelerationally independent to all practical extents. They are resistant to shock and vibration and will operate on moving vehicles or while the mobile telephone is being carried around.
  • Nucleic Acid Amplification Variants Direct PCR
  • [0316]
    Traditionally, PCR requires extensive purification of the target DNA prior to preparation of the reaction mixture. However, with appropriate changes to the chemistry and sample concentration, it is possible to perform nucleic acid amplification with minimal DNA purification, or direct amplification. When the nucleic acid amplification process is PCR, this approach is called direct PCR. In LOC devices where nucleic acid amplification is performed at a controlled, constant temperature, the approach is direct isothermal amplification. Direct nucleic acid amplification techniques have considerable advantages for use in LOC devices, particularly relating to simplification of the required fluidic design. Adjustments to the amplification chemistry for direct PCR or direct isothermal amplification include increased buffer strength, the use of polymerases which have high activity and processivity, and additives which chelate with potential polymerase inhibitors. Dilution of inhibitors present in the sample is also important.
  • [0317]
    To take advantage of direct nucleic acid amplification techniques, the LOC device designs incorporate two additional features. The first feature is reagent reservoirs (for example reservoir 58 in FIG. 8) which are appropriately dimensioned to supply a sufficient quantity of amplification reaction mix, or diluent, so that the final concentrations of sample components which might interfere with amplification chemistry are low enough to permit successful nucleic acid amplification. The desired dilution of non-cellular sample components is in the range of 5× to 20×. Different LOC structures, for example the pathogen dialysis section 70 in FIG. 4, are used when appropriate to ensure that the concentration of target nucleic acid sequences is maintained at a high enough level for amplification and detection. In this embodiment, further illustrated in FIG. 6, a dialysis section which effectively concentrates pathogens small enough to be passed into the amplification section 292 is employed upstream of the sample extraction section 290, and rejects larger cells to a waste receptacle 76. In another embodiment, a dialysis section is used to selectively deplete proteins and salts in blood plasma while retaining cells of interest.
  • [0318]
    The second LOC structural feature which supports direct nucleic acid amplification is design of channel aspect ratios to adjust the mixing ratio between the sample and the amplification mix components. For example, to ensure dilution of inhibitors associated with the sample in the preferred 5×-20× range through a single mixing step, the length and cross-section of the sample and reagent channels are designed such that the sample channel, upstream of the location where mixing is initiated, constitutes a flow impedance 4×-19× higher than the flow impedance of the channels through which the reagent mixture flows. Control over flow impedances in microchannels is readily achieved through control over the design geometry. The flow impedance of a microchannel increases linearly with the channel length, for a constant cross-section. Importantly for mixing designs, flow impedance in microchannels depends more strongly on the smallest cross-sectional dimension. For example, the flow impedance of a microchannel with rectangular cross-section is inversely proportional to the cube of the smallest perpendicular dimension, when the aspect ratio is far from unity.
  • Reverse-Transcriptase PCR (RT-PCR)
  • [0319]
    Where the sample nucleic acid species being analysed or extracted is RNA, such as from RNA viruses or messenger RNA, it is first necessary to reverse transcribe the RNA into complementary DNA (cDNA) prior to PCR amplification. The reverse transcription reaction can be performed in the same chamber as the PCR (one-step RT-PCR) or it can be performed as a separate, initial reaction (two-step RT-PCR). In the LOC variants described herein, a one-step RT-PCR can be performed simply by adding the reverse transcriptase to reagent reservoir 62 along with the polymerase and programming the heaters 154 to cycle firstly for the reverse transcription step and then progress onto the nucleic acid amplification step. A two-step RT-PCR could also be easily achieved by utilizing the reagent reservoir 58 to store and dispense the buffers, primers, dNTPs and reverse transcriptase and the incubation section 114 for the reverse transcription step followed by amplification in the normal way in the amplification section 112.
  • Isothermal Nucleic Acid Amplification
  • [0320]
    For some applications, isothermal nucleic acid amplification is the preferred method of nucleic acid amplification, thus avoiding the need to repetitively cycle the reaction components through various temperature cycles but instead maintaining the amplification section at a constant temperature, typically around 37° C. to 41° C. A number of isothermal nucleic acid amplification methods have been described, including Strand Displacement Amplification (SDA), Transcription Mediated Amplification (TMA), Nucleic Acid Sequence Based Amplification (NASBA), Recombinase Polymerase Amplification (RPA), Helicase-Dependent isothermal DNA Amplification (HDA), Rolling Circle Amplification (RCA), Ramification Amplification (RAM) and Loop-mediated Isothermal Amplification (LAMP), and any of these, or other isothermal amplification methods, can be employed in particular embodiments of the LOC device described herein.
  • [0321]
    In order to perform isothermal nucleic acid amplification, the reagent reservoirs 60 and 62 adjoining the amplification section will be loaded with the appropriate reagents for the specified isothermal method instead of PCR amplification mix and polymerase. For example, for SDA, reagent reservoir 60 contains amplification buffer, primers and dNTPs and reagent reservoir 62 contains an appropriate nickase enzyme and Exo-DNA polymerase. For RPA, reagent reservoir 60 contains the amplification buffer, primers, dNTPs and recombinase proteins, with reagent reservoir 62 containing a strand displacing DNA polymerase such as Bsu. Similarly, for HDA, reagent reservoir 60 contains amplification buffer, primers and dNTPs and reagent reservoir 62 contains an appropriate DNA polymerase and a helicase enzyme to unwind the double stranded DNA strand instead of using heat. The skilled person will appreciate that the necessary reagents can be split between the two reagent reservoirs in any manner appropriate for the nucleic acid amplification process.
  • [0322]
    For amplification of viral nucleic acids from RNA viruses such as HIV or hepatitis C virus, NASBA or TMA is appropriate as it is unnecessary to first transcribe the RNA to cDNA. In this example, reagent reservoir 60 is filled with amplification buffer, primers and dNTPs and reagent reservoir 62 is filled with RNA polymerase, reverse transcriptase and, optionally, RNase H.
  • [0323]
    For some forms of isothermal nucleic acid amplification it may be necessary to have an initial denaturation cycle to separate the double stranded DNA template, prior to maintaining the temperature for the isothermal nucleic acid amplification to proceed. This is readily achievable in all embodiments of the LOC device described herein, as the temperature of the mix in the amplification section 112 can be carefully controlled by the heaters 154 in the amplification microchannels 158 (see FIG. 14).
  • [0324]
    Isothermal nucleic acid amplification is more tolerant of potential inhibitors in the sample and, as such, is generally suitable for use where direct nucleic acid amplification from the sample is desired. Therefore, isothermal nucleic acid amplification is sometimes useful in LOC variant XLIII 673, LOC variant XLIV 674 and LOC variant XLVII 677, amongst others, shown in FIGS. 75, 76 and 77, respectively. Direct isothermal amplification may also be combined with one or more pre-amplification dialysis steps 70, 686 or 682 as shown in FIGS. 75 and 77 and/or a pre-hybridization dialysis step 682 as indicated in FIG. 76 to help partially concentrate the target cells in the sample before nucleic acid amplification or remove unwanted cellular debris prior to the sample entering the hybridization chamber array 110, respectively. The person skilled in the art will appreciate that any combination of pre-amplification dialysis and pre-hybridization dialysis can be used.
  • [0325]
    Isothermal nucleic acid amplification can also be performed in parallel amplification sections such as those schematically represented in FIGS. 71, 72 and 73, multiplexed and some methods of isothermal nucleic acid amplification, such as LAMP, are compatible with an initial reverse transcription step to amplify RNA.
  • Additional Details on the Fluorescence Detection System
  • [0326]
    FIGS. 58 and 59 show the hybridization-responsive FRET probes 236. These are often referred to as molecular beacons and are stem-and-loop probes, generated from a single strand of nucleic acid, that fluoresce upon hybridization to complementary nucleic acids. FIG. 58 shows a single FRET probe 236 prior to hybridization with a target nucleic acid sequence 238. The probe has a loop 240, stem 242, a fluorophore 246 at the 5′ end, and a quencher 248 at the 3′ end. The loop 240 consists of a sequence complementary to the target nucleic acid sequence 238. Complementary sequences on either side of the probe sequence anneal together to form the stem 242.
  • [0327]
    In the absence of a complementary target sequence, the probe remains closed as shown in FIG. 58. The stem 242 keeps the fluorophore-quencher pair in close proximity to each other, such that significant resonant energy transfer can occur between them, substantially eliminating the ability of the fluorophore to fluoresce when illuminated with the excitation light 244.
  • [0328]
    FIG. 59 shows the FRET probe 236 in an open or hybridized configuration. Upon hybridization to a complementary target nucleic acid sequence 238, the stem-and-loop structure is disrupted, the fluorophore and quencher are spatially separated, thus restoring the ability of the fluorophore 246 to fluoresce. The fluorescence emission 250 is optically detected as an indication that the probe has hybridized.
  • [0329]
    The probes hybridize with very high specificity with complementary targets, since the stem helix of the probe is designed to be more stable than a probe-target helix with a single nucleotide that is not complementary. Since double-stranded DNA is relatively rigid, it is sterically impossible for the probe-target helix and the stem helix to coexist.
  • Primer-Linked Probes
  • [0330]
    Primer-linked, stem-and-loop probes and primer-linked, linear probes, otherwise known as scorpion probes, are an alternative to molecular beacons and can be used for real-time and quantitative nucleic acid amplification in the LOC device. Real-time amplification could be performed directly in the hybridization chambers of the LOC device. The benefit of using primer-linked probes is that the probe element is physically linked to the primer, thus only requiring a single hybridization event to occur during the nucleic acid amplification rather than separate hybridizations of the primers and probes being required. This ensures that the reaction is effectively instantaneous and results in stronger signals, shorter reaction times and better discrimination than when using separate primers and probes. The probes (along with polymerase and the amplification mix) would be deposited into the hybridization chambers 180 during fabrication and there would be no need for a separate amplification section on the LOC device. Alternatively, the amplification section is left unused or used for other reactions.
  • Primer-Linked Linear Probe
  • [0331]
    FIGS. 78 and 79 show a primer-linked linear probe 692 during the initial round of nucleic acid amplification and in its hybridized configuration during subsequent rounds of nucleic acid amplification, respectively. Referring to FIG. 78, the primer-linked linear probe 692 has a double-stranded stem segment 242. One of the strands incorporates the primer linked probe sequence 696 which is homologous to a region on the target nucleic acid 696 and is labelled on its 5′ end with fluorophore 246, and linked on its 3′ end to an oligonucleotide primer 700 via an amplification blocker 694. The other strand of the stem 242 is labelled at its 3 end with a quencher moiety 248. After an initial round of nucleic acid amplification has completed, the probe can loop around and hybridize to the extended strand with the, now complementary, sequence 698. During the initial round of nucleic acid amplification, the oligonucleotide primer 700 anneals to the target DNA 238 (FIG. 78) and is then extended, forming a DNA strand containing both the probe sequence and the amplification product. The amplification blocker 694 prevents the polymerase from reading through and copying the probe region 696. Upon subsequent denaturation, the extended oligonucleotide primer 700/template hybrid is dissociated and so is the double stranded stem 242 of the primer-linked linear probe, thus releasing the quencher 248. Once the temperature decreases for the annealing and extension steps, the primer linked probe sequence 696 of the primer-linked linear probe curls around and hybridizes to the amplified complementary sequence 698 on the extended strand and fluorescence is detected indicating the presence of the target DNA. Non-extended primer-linked linear probes retain their double-stranded stem and fluorescence remains quenched. This detection method is particularly well suited for fast detection systems as it relies on a single-molecule process.
  • Primer-Linked Stem-and-Loop Probes
  • [0332]
    FIGS. 80A to 80F show the operation of a primer-linked stem-and-loop probe 704. Referring to FIG. 80A, the primer-linked stem-and-loop probe 704 has a stem 242 of complementary double-stranded DNA and a loop 240 which incorporates the probe sequence. One of the stem strands 708 is labelled at its 5′ end with fluorophore 246. The other strand 710 is labelled with a 3′-end quencher 248 and carries both the amplification blocker 694 and oligonucleotide primer 700. During the initial denaturation phase (see FIG. 80B), the strands of the target nucleic acid 238 separate, as does the stem 242 of the primer-linked, stem-and-loop probe 704. When the temperature cools for the annealing phase (see FIG. 80C), the oligonucleotide primer 700 on the primer-linked stem-and-loop probe 704 hybridizes to the target nucleic acid sequence 238. During extension (see FIG. 80D) the complement 706 to the target nucleic acid sequence 238 is synthesized forming a DNA strand containing both the probe sequence 704 and the amplified product. The amplification blocker 694 prevents the polymerase from reading through and copying the probe region 704. When the probe next anneals, following denaturation, the probe sequence of the loop segment 240 of the primer-linked stem-and-loop probe (see FIG. 80F) anneals to the complementary sequence 706 on the extended strand. This configuration leaves the fluorophore 246 relatively remote from the quencher 248, resulting in a significant increase in fluorescence emission.
  • Control Probes
  • [0333]
    The hybridization chamber array 110 includes some hybridization chambers 180 with positive and negative control probes used for assay quality control. FIGS. 92 and 93 schematically illustrate negative control probes without a fluorophore 796, and FIGS. 94 and 95 are sketches of positive control probes without a quencher 798. The positive and negative control probes have a stem-and-loop structure like the FRET probes described above. However, a fluorescence signal 250 will always be emitted from positive control probes 798 and no fluorescence signal 250 is ever emitted from negative control probes 796, regardless of whether the probes hybridize into an open configuration or remain closed.
  • [0334]
    Referring to FIGS. 92 and 93, the negative control probe 796 has no fluorophore (and may or may not have a quencher 248). Hence, whether the target nucleic acid sequence 238 hybridizes with the probe (see FIG. 93), or the probe remains in its stem-and-loop configuration (see FIG. 92), the response to the excitation light 244 is negligible. Alternatively, the negative control probe 796 could be designed so that it always remains quenched. For example, by synthesizing the loop 240 to have a probe sequence that will not hybridize to any nucleic acid sequence within the sample under investigation, the stem 242 of the probe molecule will re-hybridize to itself and the fluorophore and quencher will remain in close proximity and no appreciable fluorescence signal will be emitted. This negative control signal would correspond to low level emissions from hybridization chambers 180 in which the probes has not hybridized but the quencher does not quench all emissions from the reporter.
  • [0335]
    Conversely, the positive control probe 798 is constructed without a quencher as illustrated in FIGS. 94 and 95. Nothing quenches the fluorescence emission 250 from the fluorophore 246 in response to the excitation light 244 regardless of whether the positive control probe 798 hybridizes with the target nucleic acid sequence 238.
  • [0336]
    FIG. 52 shows a possible distribution of the positive and negative control probes (378 and 380 respectively) throughout the hybridization chamber array 110. The control probes 378 and 380 are placed in hybridization chambers 180 positioned in a line across the hybridization chamber array 110. However, the arrangement of the control probes within the array is arbitrary (as is the configuration of the hybridization chamber array 110).
  • Fluorophore Design
  • [0337]
    Fluorophores with long fluorescence lifetimes are required in order to allow enough time for the excitation light to decay to an intensity below that of the fluorescence emission at which time the photosensor 44 is enabled, thereby providing a sufficient signal to noise ratio. Also, longer fluorescence lifetime translates into larger integrated fluorescence photon count.
  • [0338]
    The fluorophores 246 (see FIG. 59) have a fluorescence lifetime greater than 100 nanoseconds, often greater than 200 nanoseconds, more commonly greater than 300 nanoseconds and in most cases greater than 400 nanoseconds.
  • [0339]
    The metal-ligand complexes based on the transition metals or lanthanides have long lifetimes (from hundreds of nanoseconds to milliseconds), adequate quantum yields, and high thermal, chemical and photochemical stability, which are all favourable properties with respect to the fluorescence detection system requirements.
  • [0340]
    A particularly well-studied metal-ligand complex based on the transition metal ion Ruthenium (Ru(II)) is tris(2,2′-bipyridine) ruthenium (II) ([Ru(bpy)3]2+) which has a lifetime of approximately 1 μs. This complex is available commercially from Biosearch Technologies under the brand name Pulsar 650.
  • [0000]
    TABLE 1
    Photophysical properties of Pulsar 650 (Ruthenium chelate)
    Parameter Symbol Value Unit
    Absorption Wavelength λabs 460 nm
    Emission Wavelength λem 650 nm
    Extinction Coefficient E 14800 M−1cm−1
    Fluorescence Lifetime τf 1.0 μs
    Quantum Yield H 1 (deoxygenated) N/A
  • [0341]
    Terbium chelate, a lanthanide metal-ligand complex has been successfully demonstrated as a fluorescent reporter in a FRET probe system, and also has a long lifetime of 1600 μs.
  • [0000]
    TABLE 2
    Photophysical properties of terbium chelate
    Parameter Symbol Value Unit
    Absorption Wavelength λabs 330-350 nm
    Emission Wavelength λem  548 nm
    Extinction Coefficient E 13800  M−1cm−1
    abs and ligand
    dependent, can be up
    to 30000 @ λe=340 nm)
    Fluorescence Lifetime τf 1600 μs
    (hybridized probe)
    Quantum Yield H   1 N/A
    (ligand dependent)
  • [0342]
    The fluorescence detection system used by the LOC device 301 does not utilize filters to remove unwanted background fluorescence. It is therefore advantageous if the quencher 248 has no native emission in order to increase the signal-to-noise ratio. With no native emission, there is no contribution to background fluorescence from the quencher 248. High quenching efficiency is also important so that fluorescence is prevented until a hybridization event occurs. The Black Hole Quenchers (BHQ), available from Biosearch Technologies, Inc. of Novato Calif., have no native emission and high quenching efficiency, and are suitable quenchers for the system. BHQ-1 has an absorption maximum at 534 nm, and a quenching range of 480-580 nm, making it a suitable quencher for the Tb-chelate fluorophore. BHQ-2 has an absorption maximum at 579 nm, and a quenching range of 560-670 nm, making it a suitable quencher for Pulsar 650.
  • [0343]
    Iowa Black Quenchers (Iowa Black FQ and RQ), available from Integrated DNA Technologies of Coralville, Iowa, are suitable alternative quenchers with little or no background emission. Iowa Black FQ has a quenching range from 420-620 nm, with an absorption maximum at 531 nm and would therefore be a suitable quencher for the Tb-chelate fluorophore. Iowa Black RQ has an absorption maximum at 656 nm, and a quenching range of 500-700 nm, making it an ideal quencher for Pulsar 650.
  • [0344]
    In the embodiments described here, the quencher 248 is a functional moiety which is initially attached to the probe, but other embodiments are possible in which the quencher is a separate molecule free in solution.
  • Excitation Source
  • [0345]
    In the fluorescence detection based embodiments described herein, a LED is chosen as the excitation source instead of a laser diode, high power lamp or laser due to the low power consumption, low cost and small size. Referring to FIG. 81, the LED 26 is positioned directly above the hybridization chamber array 110 on an external surface of the LOC device 301. On the opposing side of the hybridization chamber array 110, is the photosensor 44, made up of an array of photodiodes 184 (see FIGS. 53, 54 and 64) for detection of fluorescence signals from each of the chambers.
  • [0346]
    FIGS. 82, 83 and 84 schematically illustrate other embodiments for exposing the probes to excitation light. In the LOC device 30 shown in FIG. 82, the excitation light 244 generated by the excitation LED 26 is directed onto the hybridization chamber array 110 by the lens 254. The excitation LED 26 is pulsed and the fluorescence emissions are detected by the photosensor 44.
  • [0347]
    In the LOC device 30 shown in FIG. 83, the excitation light 244 generated by the excitation LED 26 is directed onto the hybridization chamber array 110 by the lens 254, a first optical prism 712 and second optical prism 714. The excitation LED 26 is pulsed and the fluorescence emissions are detected by the photosensor 44.
  • [0348]
    Similarly, the LOC device 30 shown in FIG. 84, the excitation light 244 generated by the excitation LED 26 is directed onto the hybridization chamber array 110 by the lens 254, a first minor 716 and second minor 718. Again, the excitation LED 26 is pulsed and the fluorescence emissions are detected by the photosensor 44.
  • [0349]
    The excitation wavelength of the LED 26 is dependent on the choice of fluorescent dye. The Philips LXK2-PR14-R00 is a suitable excitation source for the Pulsar 650 dye. The SET UVTOP335TO39BL LED is a suitable excitation source for the Tb-chelate label.
  • [0000]
    TABLE 3
    Philips LXK2-PR14-R00 LED specifications
    Parameter Symbol Value Unit
    Wavelength λex 460 nm
    Emission Frequency νem 6.52(10)14 Hz
    Output Power pl 0.515 (min) @ 1A W
    Radiation pattern Lambertian profile N/A
  • [0000]
    TABLE 4
    SET UVTOP334TO39BL LED Specifications
    Parameter Symbol Value Unit
    Wavelength λe 340 nm
    Emission Frequency νe 8.82(10)14 Hz
    Power pl 0.000240 (min) @ 20 mA W
    Pulse Forward Current I 200 mA
    Radiation pattern Lambertian N/A
  • Ultra Violet Excitation Light
  • [0350]
    Silicon absorbs little light in the UV spectrum. Accordingly, it is advantageous to use UV excitation light. A UV LED excitation source can be used but the broad spectrum of the LED 26 reduces the effectiveness of this method. To address this, a filtered UV LED can be used. Optionally, a UV laser can be the excitation source unless the relatively high cost of the laser is impractical for the particular test module market.
  • LED Driver
  • [0351]
    The LED driver 29 drives the LED 26 at a constant current for the required duration. A lower power USB 2.0-certifiable device can draw at most 1 unit load (100 mA), with a minimum operating voltage of 4.4 V. A standard power conditioning circuit is used for this purpose.
  • Photodiode
  • [0352]
    FIG. 54 shows the photodiode 184 integrated into the CMOS circuitry 86 of the LOC device 301. The photodiode 184 is fabricated as part of the CMOS circuitry 86 without additional masks or steps. This is one significant advantage of a CMOS photodiode over a CCD, an alternate sensing technology which could be integrated on the same chip using non-standard processing steps, or fabricated on an adjacent chip. On-chip detection is low cost and reduces the size of the assay system. The shorter optical path length reduces noise from the surrounding environment for efficient collection of the fluorescence signal and eliminates the need for a conventional optical assembly of lenses and filters.
  • [0353]
    Quantum efficiency of the photodiode 184 is the fraction of photons impinging on its active area 185 that are effectively converted to photo-electrons. For standard silicon processes, the quantum efficiency is in the range of 0.3 to 0.5 for visible light, depending on process parameters such as the amount and absorption properties of the cover layers.
  • [0354]
    The detection threshold of the photodiode 184 determines the smallest intensity of the fluorescence signal that can be detected. The detection threshold also determines the size of the photodiode 184 and hence the number of hybridization chambers 180 in the hybridization and detection section 52 (see FIG. 52). The size and number of chambers are technical parameters that are limited by the dimensions of the LOC device (in the case of the LOC device 301, the dimensions are 1760 μm×5824 μm) and the real estate available after other functional modules such as the pathogen dialysis section 70 and amplification section(s) 112 are incorporated.
  • [0355]
    For standard silicon processes, the photodiode 184 detects a minimum of 5 photons. However, to ensure reliable detection, the minimum can be set to 10 photons. Therefore with the quantum efficiency range being 0.3 to 0.5 (as discussed above), the fluorescence emission from the probes should be a minimum of 17 photons but 30 photons would incorporate a suitable margin of error for reliable detection.
  • Calibration Chambers
  • [0356]
    The non-uniformity of the electrical characteristic of the photodiode 184, autofluorescence, and residual excitation photon flux that has not yet completely decayed, introduce background noise and offset into the output signal. This background is removed from each output signal using one or more calibration signals. Calibration signals are generated by exposing one or more calibration photodiodes 184 in the array to respective calibration sources. A low calibration source is used for determining a negative result in which a target has not reacted with a probe. A high calibration source is indicative of a positive result from a probe-target complex. In the embodiment described here, the low calibration light source is provided by calibration chambers 382 in the hybridization chamber array 110 which:
  • [0357]
    do not contain any probes;
  • [0358]
    contain probes that have no fluorescent reporter; or,
  • [0359]
    contain probes with a reporter and quencher configured such that quenching is always expected to occur.
  • [0360]
    The output signal from such calibration chambers 382 closely approximates the noise and offset in the output signal from all the hybridization chambers in the LOC device. Subtracting the calibration signal from the output signals generated by the other hybridization chambers substantially removes the background and leaves the signal generated by the fluorescence emission (if any). Signals arising from ambient light in the region of the chamber array are also subtracted.
  • [0361]
    It will be appreciated that the negative control probes described above with reference to FIGS. 92 to 95 can be be used in calibration chambers. However, as shown in FIGS. 86 and 87, which are enlarged views of insets DG and DH of LOC variant X 728 shown in FIG. 85, another option is to fluidically isolate the calibration chambers 382 from the amplicon. The background noise and offset can be determined by leaving the fluidically isolated chambers empty, or containing reporterless probes, or indeed any of the ‘normal’ probes with both reporter and quencher as hybridization is precluded by fluidic isolation.
  • [0362]
    The calibration chambers 382 can provide a high calibration source to generate a high signal in the corresponding photodiodes. The high signal corresponds to all probes in a chamber having hybridized. Spotting probes with reporters and no quenchers, or just reporters will consistently provide a signal approximating that of a hybridization chamber in which a predominant number of the probes have hybridized. It will also be appreciated that calibration chambers 382 can be used instead of control probes, or in addition to control probes.
  • [0363]
    The number and arrangement of the calibration chambers 382 throughout the hybridization chamber array is arbitrary. However, the calibration is more accurate if photodiodes 184 are calibrated by a calibration chamber 382 that is relatively proximate. Referring to FIG. 56, the hybridization chamber array 110 has one calibration chamber 382 for every eight hybridization chambers 180. That is, a calibration chamber 382 is positioned in the middle of every three by three square of hybridization chambers 180. In this configuration, the hybridization chambers 180 are calibrated by a calibration chamber 382 that is immediately adjacent.
  • [0364]
    FIG. 91 shows a differential imager circuit 788 used to substract the signal from the photodiode 184 corresponding to the calibration chamber 382 as a result of excitation light, from the fluorescence signal from the surrounding hybridization chambers 180. The differential imager circuit 788 samples the signal from the pixel 790 and a “dummy” pixel 792. In one embodiment, the “dummy” pixel 792 is shielded from light, so its output signal provides a dark reference. Alternatively, the “dummy” pixel 792 can be exposed to the excitation light along with the rest of the array. In the embodiment where the “dummy” pixel 792 is open to light, signals arising from ambient light in the region of the chamber array are also subtracted. The signals from the pixel 790 are small (i.e. close to dark signal), and without a reference to a dark level it is hard to differentiate between the background and a very small signal.
  • [0365]
    During use, the “read_row” 794 and “read_row_d” 795 are activated and M4 797 and MD4 801 transistors are turned on. Switches 807 and 809 are closed such that the outputs from the pixel 790 and “dummy” pixel 792 are stored on pixel capacitor 803 and dummy pixel capacitor 805 respectively. After the pixel signals have been stored, switches 807 and 809 are deactivated. Then the “read_col” switch 811 and dummy “read_col” switch 813 are closed, and the switched capacitor amplifier 815 at the output amplifies the differential signal 817.
  • Suppression and Enablement of the Photodiode
  • [0366]
    The photodiode 184 needs to be suppressed during excitation by the LED 26 and enabled during fluorescence. FIG. 65 is a circuit diagram for a single photodiode 184 and FIG. 66 is a timing diagram for the photodiode control signals. The circuit has photodiode 184 and six MOS transistors, Mshunt 394, Mtx 396, Mreset 398, Msf 400, Mread 402 and Mbias 404. At the beginning of the excitation cycle, t1, the transistors Mshunt 394, and Mreset 398 are turned on by pulling the Mshunt gate 384 and the reset gate 388 high. During this period, the excitation photons generate carriers in the photodiode 184. These carriers have to be removed, as the amount of generated carriers can be sufficient to saturate the photodiode 184. During this cycle, Mshunt 394 directly removes the carriers generated in photodiode 184, while Mreset 398 resets any carriers that have accumulated on node ‘NS’ 406 due to leakage in transistors or due to diffusion of excitation-produced carriers in the substrate. After excitation, a capture cycle commences at t4. During this cycle, the emitted response from the fluorophore is captured and integrated in the circuit on node ‘NS’ 406. This is achieved by pulling tx gate 386 high, which turns on the transistor Mtx 396 and transfers any accumulated carriers on the photodiode 184 to node ‘NS’ 406. The duration of the capture cycle can be as long as the fluorophore emits. The outputs from all photodiodes 184 in the hybridization chamber array 110 are captured simultaneously. There is a delay between the end of the capture cycle t5 and the start of the read cycle t6.
  • [0367]
    This delay is due to the requirement to read each photodiode 184 in the hybridization chamber array 110 (see FIG. 52) separately following the capture cycle. The first photodiode 184 to be read will have the shortest delay before the read cycle, while the last photodiode 184 will have the longest delay before the read cycle. During the read cycle, transistor Mread 402 is turned on by pulling the read gate 393 high. The ‘NS’ node 406 voltage is buffered and read out using the source-follower transistor Msf 400.
  • [0368]
    There are additional, optional methods of enabling or suppressing the photodiode as discussed below:
  • 1. Suppression Methods
  • [0369]
    FIGS. 88, 89 and 90 show three possible configurations 778, 780, 782 for the Mshunt transistor 394. The Mshunt transistor 394 has a very high off ratio at maximum |VGS|=5 V which is enabled during excitation. As shown in FIG. 88, the Mshunt gate 384 is configured to be on the edge of the photodiode 184. Optionally, as shown in FIG. 89, the Mshunt gate 384 may be configured to surround the photodiode 184. A third option is to configure the Mshunt gate 384 inside the photodiode 184, as shown in FIG. 90. Under this third option there would be less photodiode active area 185.
  • [0370]
    These three configurations 778, 780 and 782 reduce the average path length from all locations in the photodiode 184 to the Mshunt gate 384. In FIG. 88, the Mshunt gate 384 is on one side of the photodiode 184. This configuration is simplest to fabricate and impinges the least on the photodiode active area 185. However, any carriers lingering on the remote side of the photodiode 184 would take longer to propagate through to the Mshunt gate 384.
  • [0371]
    In FIG. 89, the Mshunt gate 384 surrounds the photodiode 184. This further reduces the average path length for carriers in the photodiode 184 to the Mshunt gate 384. However, extending the Mshunt gate 384 about the periphery of the photodiode 184 imposes a greater reduction of the photodiode active area 185. The configuration 782 in FIG. 90 positions the Mshunt gate 384 within the active area 185. This provides the shortest average path length to the Mshunt gate 384 and hence the shortest transition time. However, the impingement on the active area 185 is greatest. It also poses a wider leakage path.
  • 2. Enabling Methods
  • [0372]
    a. A trigger photodiode drives the shunt transistor with a fixed delay.
    b. A trigger photodiode drives the shunt transistor with programmable delay.
    c. The shunt transistor is driven from the LED drive pulse with a fixed delay.
    d. The shunt transistor is driven as in 2c but with programmable delay.
  • [0373]
    FIG. 68 is a schematic section view through a hybridization chamber 180 showing a photodiode 184 and trigger photodiode 187 embedded in the CMOS circuitry 86. A small area in the corner of the photodiode 184 is replaced with the trigger photodiode 187. A trigger photodiode 187 with a small area is sufficient as the intensity of the excitation light will be high in comparison with the fluorescence emission. The trigger photodiode 187 is sensitive to the excitation light 244. The trigger photodiode 187 registers that the excitation light 244 has extinguished and activates the photodiode 184 after a short time delay Δt 300 (see FIG. 2). This delay allows the fluorescence photodiode 184 to detect the fluorescence emission from the FRET probes 186 in the absence of the excitation light 244. This enables detection and improves the signal to noise ratio.
  • [0374]
    Both photodiodes 184 and trigger photodiodes 187 are located in the CMOS circuitry 86 under each hybridization chamber 180. The array of photodiodes combines, along with appropriate electronics, to form the photosensor 44 (see FIG. 64). The photodiodes 184 are pn-junction fabricated during CMOS structure manufacturing without additional masks or steps. During MST fabrication, the dielectric layer (not shown) above the photodiodes 184 is optionally thinned using the standard MST photolithography techniques to allow more fluorescent light to illuminate the active area 185 of the photodiode 184. The photodiode 184 has a field of view such that the fluorescence signal from the probe-target hybrids within the hybridization chamber 180 is incident on the sensor face. The fluorescent light is converted into a photocurrent which can then be measured using CMOS circuitry 86.
  • [0375]
    Alternatively, one or more hybridization chambers 180 can be dedicated to a trigger photodiode 187 only. These options can be used in these in combination with 2a and 2b above.
  • Delayed Detection of Fluorescence
  • [0376]
    The following derivations elucidate the delayed detection of fluorescence using a long-lifetime fluorophore for the LED/fluorophore combinations described above. The fluorescence intensity is derived as a function of time after excitation by an ideal pulse of constant intensity I, between time t1 and t2 as shown in FIG. 60.
  • [0377]
    Let [S1](t) equal the density of excited states at time t, then during and after excitation, the number of excited states per unit time per unit volume is described by the following differential equation:
  • [0000]
    [ S 1 ] t ( t ) + [ S 1 ] ( t ) τ F = I e ɛ c hv e ( 1 )
  • [0000]
    where c is the molar concentration of fluorophores, E is the molar extinction coefficient, νe is the excitation frequency, and h=6.62606896(10)−34 Js is the Planck constant.
    This differential equation has the general form:
  • [0000]
    y x + p ( x ) y = q ( x )
  • [0000]
    which has the solution:
  • [0000]
    y ( x ) = p ( x ) x q ( x ) x + k p ( x ) x ( 2 )
  • [0378]
    Using this now to solve equation (1),
  • [0000]
    [ S 1 ] ( t ) = I e ɛ c τ f hv e + k - t / τ f ( 3 )
  • [0379]
    Now at time t1, [S1](t1)=0, and from (3):
  • [0000]
    k = - I e ɛ c τ f hv e t 1 / τ f ( 4 )
  • [0380]
    Substituting (4) into (3):
  • [0000]
    [ S 1 ] ( t ) = I e ɛ c τ f hv e - I e ɛ c τ f hv e - ( t - t 1 ) / τ f
  • [0381]
    At time t2,:
  • [0000]
    [ S 1 ] ( t 2 ) = I e ɛ c τ f hv e - I e ɛ c τ f hv e - ( t 2 - t 1 ) / τ f ( 5 )
  • [0382]
    For t≧t2, the excited states decay exponentially and this is described by:
  • [0000]

    [S1](t)=[S1](t 2)e −(t-t 2 )/τ f   (6)
  • [0383]
    Substituting (5) into (6):
  • [0000]
    [ S 1 ] ( t ) = I e ɛ c τ f hv e [ 1 - - ( t 2 - t 1 ) / τ f ] - ( t - t 2 ) / τ f ( 7 )
  • [0384]
    The fluorescence intensity is given by the following equation:
  • [0000]
    I f ( t ) = - [ S 1 ] ( t ) x hv f η l ( 8 )
  • [0000]
    where νf is the fluorescence frequency, η is the quantum yield and 1 is the optical path length.
  • [0385]
    Now from (7):
  • [0000]
    [ S 1 ] ( t ) t = - I e ɛ c hv e [ 1 - - ( t 2 - t 1 ) / τ f ] - ( t - t 2 ) / τ f ( 9 )
  • [0386]
    Substituting (9) into (8):
  • [0000]
    I f ( t ) = I e ɛ cl η v f v e [ 1 - - ( t 2 - t 1 ) / τ f ] - ( t - t 2 ) / τ f For t 2 - t 1 τ f -> , I f ( t ) -> I e ɛ cl η v f v e - ( t - t 2 ) / τ f ( 10 )
  • [0387]
    Therefore, we can write the following approximate equation which describes the fluorescence intensity decay after a sufficiently long excitation pulse (t2−t1>>τf):
  • [0000]
    I f ( t ) = I e ɛ cl η v f v e - ( t - t 2 ) / τ f for t t 2 ( 11 )
  • [0388]
    In the previous section, we concluded that for t2−t1>>τf,
  • [0000]
    I f ( t ) = I e ɛ cl η v f v e - ( t - t 2 ) / τ f for t t 2 .
  • [0389]
    From the above equation, we can derive the following:
  • [0000]
    n f ( t ) = n e ɛ cl η - ( t - t 2 ) / τ f where n f ( t ) = I f ( t ) hv f ( 12 )
  • [0000]
    is the number of fluorescent photons per unit time per unit area and
  • [0000]
    n e = I e hv e
  • [0000]
    is the number of excitation photons per unit time per unit area.
  • [0390]
    Consequently,
  • [0000]
    n ¨ f ( t ) = t 3 n f ( t ) t ( 13 )
  • [0000]
    where {umlaut over (n)}f is the number of fluorescent photons per unit area and t3 is the instant of time at which the photodiode is turned on. Substituting (12) into (13):
  • [0000]
    n ¨ f = t 3 n e ɛ cl η - ( t - t 2 ) / τ f t ( 14 )
  • [0391]
    Now, the number of fluorescent photons that reach the photodiode per unit time per unit area,
    Figure US20110312802A1-20111222-P00001
    (t), is given by the following:
  • [0000]
    n s ( t ) = n f ( t ) φ 0 ( 15 )
  • [0000]
    where φ0 is the light gathering efficiency of the optical system.
  • [0392]
    Substituting (12) into (15) we find
  • [0000]
    n s ( t ) = φ 0 n e ɛ cl η - ( t - t 2 ) / τ f ( 16 )
  • [0393]
    Similarly, the number of fluorescence photons that reach the photodiode per unit fluorescent area {umlaut over (n)}s, will be as follows:
  • [0000]
    n ¨ s = t 3 n s ( t ) t
  • [0000]
    and substituting in (16) and integrating:
  • [0000]
    n ¨ s = φ 0 n e ɛ cl η τ f - ( t 3 - t 2 ) / τ f
  • [0394]
    Therefore,
  • [0000]

    n s0 {dot over (n)} e ∈clητ f e −Δt/τ f   (17)
  • [0395]
    The optimal value of t3 is when the rate of electrons generated in the photodiode 184 due to fluorescence photons becomes equal to the rate of electrons generated in the photodiode 184 by the excitation photons, as the flux of the excitation photons decays much faster than that of the fluorescence photons.
  • [0396]
    The rate of sensor output electrons per unit fluorescent area due to fluorescence is:
  • [0000]
    e f ( t ) = φ f n s ( t )
  • [0000]
    where φf is the quantum efficiency of the sensor at the fluorescence wavelength.
  • [0397]
    Substituting in (17) we have:
  • [0000]
    e f ( t ) = φ f φ 0 n e ɛ cl η - ( t - t 2 ) / τ f ( 18 )
  • [0398]
    Similarly, the rate of sensor output electrons per unit fluorescent area due to the excitation photons is:
  • [0000]
    e e ( t ) = φ e n e - ( t - t 2 ) / τ e ( 19 )
  • [0000]
    where φe is the quantum efficiency of the sensor at the excitation wavelength, and τe is the time-constant corresponding to the “off” characteristics of the excitation LED. After time t2, the LED's decaying photon flux would increase the intensity of the fluorescence signal and extend its decay time, but we are assuming that this has a negligible effect on If(t), thus we are taking a conservative approach.
  • [0399]
    Now, as mentioned earlier, the optimal value of t3 is when:
  • [0000]
    e f ( t 3 ) = e e ( t 3 )
  • [0400]
    Therefore, from (18) and (19) we have:
  • [0000]
    φ f φ 0 n e ɛ cl η - ( t 3 - t 2 ) / τ f = φ e n e - ( t 3 - t 2 ) / τ e
  • [0000]
    and rearranging we find:
  • [0000]
    t 3 - t 2 = ln ( ɛ cl η φ f φ 0 φ e ) 1 τ f - 1 τ e ( 20 )
  • [0401]
    From the previous two sections, we have the following two working equations:
  • [0000]
    n s = φ 0 n . e F τ f - Δ t / τ f ( 21 ) Δ t = ln ( F φ f φ 0 φ e ) 1 τ f - 1 τ e ( 22 )
  • [0000]
    where F=∈clη and Δt=t3−t2. We also know that, in practice, t2−t1>>τf.
  • [0402]
    The optimal time for fluorescence detection and the number of fluorescence photons detected using the Philips LXK2-PR14-R00 LED and Pulsar 650 dye are determined as follows. The optimum detection time is determined using equation (22):
  • [0403]
    Recalling the concentration of amplicon, and assuming that all amplicons hybridize, then the concentration of fluorescent fluorophores is: c=2.89(10)−6 mol/L
  • [0404]
    The height of the chamber is the optical path length l=8(10)−6 m.
  • [0405]
    We have taken the fluorescence area to be equal to our photodiode area, yet our actual fluorescence area is substantially larger than our photodiode area; consequently we can approximately assume φ0=0.5 for the light gathering efficiency of our optical system. From the photodiode characteristics
  • [0000]
    φ f φ e = 10
  • [0000]
    is a very conservative value for the ratio of the photodiode quantum efficiency at the fluorescence wavelength to its quantum efficiency at the excitation wavelength.
  • [0406]
    With a typical LED decay lifetime of τe=0.5 ns and using Pulsar 650 specifications, Δt can be determined:
  • [0000]
    F = [ 1.48 ( 10 ) 6 ] [ 2.89 ( 10 ) - 6 ] [ 8 ( 10 ) - 6 ] ( 1 ) = 3.42 ( 10 ) - 5 Δ t = ln ( [ 3.42 ( 10 ) - 5 ] ( 10 ) ( 0.5 ) ) 1 1 ( 10 ) - 6 - 1 0.5 ( 10 ) - 9 = 4.34 ( 10 ) - 9 s
  • [0407]
    The number of photons detected is determined using equation (21). First, the number of excitation photons emitted per unit time {dot over (n)}e is determined by examining the illumination geometry.
  • [0408]
    The Philips LXK2-PR14-R00 LED has a Lambertian radiation pattern, therefore:
  • [0000]
    n l = n l 0 cos ( θ ) ( 23 )
  • [0000]
    where
    Figure US20110312802A1-20111222-P00002
    the number of photons emitted per unit time per unit solid angle at an angle of θ off the LED's forward axial direction, and
    Figure US20110312802A1-20111222-P00003
    is the valve of
    Figure US20110312802A1-20111222-P00004
    in the forward axial direction.
  • [0409]
    The total number of photons emitted by the LED per unit time is:
  • [0000]
    n . l = Ω n l Ω = Ω n l 0 cos ( θ ) Ω Now , ΔΩ = 2 π [ 1 - cos ( θ + Δθ ) ] - 2 π [ 1 - cos ( θ ) ] ΔΩ = 2 π [ cos ( θ ) - cos ( θ + Δθ ) ] = 4 πsin ( θ ) cos ( Δθ 2 ) sin ( Δθ 2 ) + 4 πcos ( θ ) sin 2 ( Δθ 2 ) Ω = 2 πsin ( θ ) Ω ( 24 )
  • [0410]
    Substituting this into (24):
  • [0000]
    n . l = 0 π 2 2 π n l 0 cos ( θ ) sin ( θ ) θ = π n l 0
  • [0411]
    Rearranging, we have:
  • [0000]
    n l 0 = n . l π ( 26 )
  • [0412]
    The LED's output power is 0.515 W and νe=6.52(10)14 Hz, therefore:
  • [0000]
    n . l = p l hv e = 0.515 [ 6.63 ( 10 ) - 34 ] [ 6.52 ( 10 ) 14 ] = 1.19 ( 10 ) 18 photons / s ( 27 )
  • [0413]
    Substituting this value into (26) we have:
  • [0000]
    n l 0 = 1.19 ( 10 ) 18 π = 3.79 ( 10 ) 17 photons / s / sr
  • [0414]
    Referring to FIG. 61, the optical centre 252 and the lens 254 of the LED 26 are schematically shown. The photodiodes are 16 μm×16 μm, and for the photodiode in the middle of the array, the solid angle (Ω) of the cone of light emitted from the LED 26 to the photodiode 184 is approximately:
  • [0000]
    Ω = area of sensor / r 2 = [ 16 ( 10 ) - 6 ] [ 16 ( 10 ) - 6 ] [ 2.825 ( 10 ) - 3 ] 2 = 3.21 ( 10 ) - 5 sr
  • [0415]
    It will be appreciated that the central photodiode 184 of the photodiode array 44 is used for the purpose of these calculations. A sensor located at the edge of the array would only receive 2% less photons upon a hybridization event for a Lambertian excitation source intensity distribution.
  • [0416]
    The number of excitation photons emitted per unit time is:
  • [0000]
    n . e = n l Ω = [ 3.79 ( 10 ) 17 ] [ 3.21 ( 10 ) - 5 ] = 1.22 ( 10 ) 13 photons / s ( 28 )
  • [0417]
    Now referring to equation (29):
  • [0000]
    n s = φ 0 n . e F τ f - Δ t / τ f n s = ( 0.5 ) [ 1.22 ( 10 ) 13 ] [ 3.42 ( 10 ) - 5 ] [ 1 ( 10 ) - 6 ] - 4.34 ( 10 ) - 9 / 1 ( 10 ) - 6 = 208 photons per sensor .
  • [0418]
    Therefore, using the Philips LXK2-PR14-R00 LED and Pulsar 650 fluorophore, we can easily detect any hybridization events which results in this number of photons being emitted.
  • [0419]
    The SET LED illumination geometry is shown in FIG. 62. At ID=20 mA, the LED has a minimum optical power output of p1=240 μW centred at λe=340 nm (the absorption wavelength of the terbium chelate). Driving the LED at ID=200 mA would increase the output power linearly to p1=2.4 mW. By placing the LED's optical centre 252, 17.5 mm away from the hybridization chamber array 110, we would approximately concentrate this output flux in a circular spot size which has a maximum diameter of 2 mm.
  • [0420]
    The photon flux in the 2 mm-diameter spot at the hybridization away plane is given by equation 27.
  • [0000]
    n . l = p l hv e = 2.4 ( 10 ) - 3 [ 6.63 ( 10 ) - 34 ] [ 8.82 ( 10 ) 14 ] = 4.10 ( 10 ) 15 photons / s
  • [0421]
    Using equation 28, we have:
  • [0000]
    n . e = n l Ω = 4.10 ( 10 ) 15 [ 16 ( 10 ) - 6 ] 2 π [ 1 ( 10 ) - 3 ] 2 = 3.34 ( 10 ) 11 photons / s
  • [0422]
    Now, recalling equation 22 and using the Tb chelate properties listed previously,
  • [0000]
    Δ t = ln [ ( 6.94 ( 10 ) - 5 ) ( 10 ) ( 0.5 ) ] 1 1 ( 10 ) - 3 - 1 0.5 ( 10 ) - 9 = 3.98 ( 10 ) - 9 s
  • [0423]
    Now from equation 21:
  • [0000]
    n s = ( 0.5 ) [ 3.34 ( 10 ) 11 ] [ 6.94 ( 10 ) - 5 ] [ 1 ( 10 ) - 3 ] - 3.98 ( 10 ) - 9 / 1 ( 10 ) - 3 = 11 , 600 photons per sensor .
  • [0424]
    The theoretical number of photons emitted by hybridization events using the SET LED and terbium chelate system are easily detectable and well over the minimum of 30 photons required for reliable detection by the photosensor as indicated above.
  • Maximum Spacing Between Probes and Photodiode
  • [0425]
    The on-chip detection of hybridization avoids the needs for detection via confocal microscopy (see Background of the Invention). This departure from traditional detection techniques is a significant factor in the time and cost savings associated with this system. Traditional detection requires imaging optics which necessarily uses lenses or curved mirrors. By adopting non-imaging optics, the diagnostic system avoids the need for a complex and bulky optical train. Positioning the photodiode very close to the probes has the advantage of extremely high collection efficiency: when the thickness of the material between the probes and the photodiode is of the order of 1 micron, the angle of collection of emission light is up to 173°. This angle is calculated by considering light emitted from a probe at the centroid of the face of the hybridization chamber closest to the photodiode, which has a planar active surface area parallel to that chamber face. The cone of emission angles within which light is able to be absorbed by the photodiode is defined as having the emitting probe at its vertex and the corner of the sensor on the perimeter of its planar face. For a 16 micron×16 micron sensor, the vertex angle of this cone is 170°; in the limiting case where the photodiode is expanded so that its area matches that of the 29 micron×19.75 micron hybridization chamber, the vertex angle is 173°. A separation between the chamber face and the photodiode active surface of 1 micron or less is readily achievable.
  • [0426]
    Employing a non-imaging optics scheme does require the photodiode 184 to be very close to the hybridization chamber in order to collect sufficient photons of fluorescence emission. The maximum spacing between the photodiode and probes is determined as follows with reference to FIG. 54.
  • [0427]
    Utilizing a terbium chelate fluorophore and a SET UVTOP335TO39BL LED, we calculated 11600 photons reaching our 16 micron×16 micron photodiode 184 from the respective hybridization chamber 180. In performing this calculation we assumed that the light-collecting region of our hybridization chamber 180 has a base area which is the same as our photodiode active area 185, and half of the total number of the hybridization photons reaches the photodiode 184. That is, the light gathering efficiency of the optical system is φ0=0.5.
  • [0428]
    More accurately we can write φ0=[(base area of the light-collecting region of the hybridization chamber)/(photodiode area)][φ/4π], where Ω=solid angle subtended by the photodiode at a representative point on the base of the hybridization chamber. For a right square pyramid geometry:
  • [0000]
    Ω=4 arcsin(a2/(4d0 2+a2)), where d0=distance between the chamber and the photodiode, and a is the photodiode dimension.
  • [0429]
    Each hybridization chamber releases 23200 photons. The selected photodiode has a detection threshold of 17 photons; therefore, the minimum optical efficiency required is:
  • [0000]

    φ0=17/23200=7.33×10−4
  • [0430]
    The base area of the light-collecting region of the hybridization chamber 180 is 29 micron×19.75 micron.
  • [0431]
    Solving for d0, we will get the maximum limiting distance between the bottom of our hybridization chamber and our photodiode 184 to be d0=249 microns. In this limit, the collection cone angle as defined above is only 0.8°. It should be noted this analysis ignores the negligible effect of refraction.
  • CONCLUSION
  • [0432]
    The devices, systems and methods described here facilitate molecular diagnostic tests at low cost with high speed and at the point-of-care.
  • [0000]
    The system and its components described above are purely illustrative and the skilled worker in this field will readily recognize many variations and modifications which do not depart from the spirit and scope of the broad inventive concept.

Claims (20)

  1. 1. A test module comprising:
    an outer casing having an inlet for receiving a biological sample containing a target nucleic acid sequence; and,
    probes in the outer casing for hybridization with the target nucleic acid sequence to form probe-target hybrids, the probes each having a fluorophore such that the probe-target hybrids emit a fluorescence signal in response to exposure to an excitation light; wherein,
    the probes are suspended in a fluid.
  2. 2. The test module according to claim 1 wherein the mass of the probes is less than 270 picograms.
  3. 3. The test module according to claim 1 further comprising a hybridization chamber mounted in the casing for containing probes wherein the hybridization chamber has a volume less than 9,000 cubic microns.
  4. 4. The test module according to claim 3 wherein and the hybridization chamber has an optical window for exposing the probes to the excitation light.
  5. 5. The test module according to claim 4 further comprising a light source for generating the excitation light and a photodiode for sensing the fluorescent response.
  6. 6. The test module according to claim 5 wherein the light source is an excitation LED mounted in the casing for emitting light through the optical window.
  7. 7. The test module according to claim 6 further comprising control circuitry for operative control of the excitation LED.
  8. 8. The test module according to claim 7 wherein the control circuitry controls activation and deactivation of the excitation LED, and conditioning of power supplied to the excitation light.
  9. 9. The test module of claim 8 wherein the control circuitry is configured to deactivate the excitation light and subsequently activate the photodiode after a time delay.
  10. 10. The test module according to claim 9 wherein the control circuitry further comprises a shunt transistor between the photodiode anode and a voltage source, the shunt transistor being configured to remove carriers generated by absorption of photons of the excitation light in the photodiode.
  11. 11. The test module according to claim 10 wherein the shunt transistor is configured to turn on when the excitation light activates and turn off when the excitation light deactivates.
  12. 12. The test module according to claim 5 further comprising an array of hybridization chambers containing different types of the probes, the probes being fluorescence resonance energy transfer (FRET) probes configured for hybridization with different target nucleic acid sequences, and an array of the photodiodes such that each of the hybridization chambers corresponds to a respective one of the photodiodes.
  13. 13. The test module according to claim 12 further comprising a polymerase chain reaction (PCR) section for amplifying the target nucleic acid sequences in the sample prior to hybridization with the FRET probes.
  14. 14. The test module according to claim 13 further comprising a microfluidic device mounted in the outer casing adjacent the excitation LED, the microfluidic device having a supporting substrate, CMOS circuitry on the supporting substrate and a microsystems technology (MST) layer on the CMOS circuitry wherein the PCR section and the hybridization chambers are incorporated in the MST layer which has a plurality of channels configured to draw the fluid through the PCR section and into the hybridization chambers by capillary action.
  15. 15. The test module according to claim 14 further comprising an electrical connection for communication to an external device wherein the CMOS circuitry is configured to convert output from the photodiodes into a signal indicative of the FRET probes that hybridized with the target nucleic acid sequences, and provide the signal to the electrical connection for transmission to the external device.
  16. 16. The test module according to claim 14 wherein the CMOS circuitry has memory for identity data for the different FRET probe types.
  17. 17. The test module according to claim 16 wherein the CMOS circuitry includes the array of photodiodes such that the array of photodiodes is less than 249 microns from the FRET probes.
  18. 18. The test module according to claim 1 wherein the fluorophore has a fluorescence lifetime greater than 100 nanoseconds.
  19. 19. The test module according to claim 11 wherein the FRET probes have a quencher to suppress the fluorescence signal from the fluorophore when the probe is in a non-hybridized configuration, the quencher having no native emission in response to the excitation light.
  20. 20. The test module according to claim 12 wherein the CMOS circuitry is configured for temperature control of the hybridization chambers during hybridization of the probes and the target nucleic acid sequences.
US13150228 2010-06-17 2011-06-01 Test module with probes suspended in fluid Abandoned US20110312802A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US35601810 true 2010-06-17 2010-06-17
US201161437686 true 2011-01-30 2011-01-30
US13150228 US20110312802A1 (en) 2010-06-17 2011-06-01 Test module with probes suspended in fluid

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US13150228 US20110312802A1 (en) 2010-06-17 2011-06-01 Test module with probes suspended in fluid

Publications (1)

Publication Number Publication Date
US20110312802A1 true true US20110312802A1 (en) 2011-12-22

Family

ID=45327470

Family Applications (355)

Application Number Title Priority Date Filing Date
US13149948 Abandoned US20110312654A1 (en) 2010-06-17 2011-06-01 Apparatus for loading oligonucleotide spotting devices and spotting oligonucleotide probes
US13149951 Abandoned US20110312656A1 (en) 2010-06-17 2011-06-01 Microfluidic device for pcr and probe hybridization
US13149890 Abandoned US20110312622A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume hybridization chambers for electrochemiluminescent detection of target sequences
US13150007 Abandoned US20110312559A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis and parallel nucleic acid amplification
US13150082 Abandoned US20110312735A1 (en) 2010-06-17 2011-06-01 Microfluidic device with nucleic acid amplification section
US13150109 Abandoned US20110312753A1 (en) 2010-06-17 2011-06-01 Loc with integral led driver for excitation led
US13150112 Abandoned US20110312756A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low reagent volumes
US13150035 Abandoned US20110312703A1 (en) 2010-06-17 2011-06-01 Microfluidic device for rapid pcr amplification
US13150160 Abandoned US20110312845A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with laminar structure
US13150200 Abandoned US20110312793A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with low mass of probes
US13150269 Abandoned US20110312838A1 (en) 2010-06-17 2011-06-01 Microfluidic device with electrochemiluminescent probes and integrated photosensor for detection of target molecules
US13149893 Abandoned US20110312545A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, chemical lysis and tandem nucleic acid amplification
US13149919 Abandoned US20110312073A1 (en) 2010-06-17 2011-06-01 Microfluidic test module incorporating surface micro-machined chips and interconnecting cap
US13150036 Abandoned US20110312571A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis and parallel nucleic acid amplification
US13150055 Abandoned US20110312717A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, incubation and nucleic acid amplification
US13150170 Abandoned US20110312781A1 (en) 2010-06-17 2011-06-01 Loc with digital memory to store genetic data updates
US13149916 Abandoned US20110312072A1 (en) 2010-06-17 2011-06-01 Microfluidic device with surface micro-machined chips and interconnecting cap
US13150271 Abandoned US20110312840A1 (en) 2010-06-17 2011-06-01 Microfluidic device with sample inlet, electrochemiluminescent probes and integrated photosensor for detection of target sequences
US13149929 Abandoned US20110311411A1 (en) 2010-06-17 2011-06-01 Microfluidic thermal bend actuated surface tension valve
US13150110 Abandoned US20110312754A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of mitochondrial dna via electrochemiluminescence modulated hybridization
US13150152 Abandoned US20110312844A1 (en) 2010-06-17 2011-06-01 Biochemical deposition device
US13150262 Abandoned US20110312831A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequence with electrochemiluminescent metalorganic complex
US13149917 Abandoned US20110312637A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for separating pathogens from a biological sample
US13150097 Abandoned US20110312744A1 (en) 2010-06-17 2011-06-01 Microfluidic device for amplifying mitochondrial dna in a biological sample
US13150230 Abandoned US20110312804A1 (en) 2010-06-17 2011-06-01 Microfluidic device with aperture with geometry to promote unpinned flow-through of fluid
US13150264 Abandoned US20110312833A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target sequences using transparent electrodes
US13149980 Abandoned US20110312679A1 (en) 2010-06-17 2011-06-01 Microfluidic device with surface-micromachined dialysis section
US13150124 Abandoned US20110312766A1 (en) 2010-06-17 2011-06-01 Microfluidic device with feedback controlled incubation section
US13150138 Abandoned US20110312772A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with pcr amplification using linker primers
US13150166 Abandoned US20110312079A1 (en) 2010-06-17 2011-06-01 Loc with digital memory to store epidemiological updates
US13150169 Abandoned US20110312780A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with negative control chambers incorporating probes with no reporters
US13150184 Expired - Fee Related US8425845B2 (en) 2010-06-17 2011-06-01 Genetic analysis LOC with hybridization array with calibration chamber containing probe that lacks a reporter
US13149953 Abandoned US20110312658A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for concentrating nucleated cells in a biological sample
US13150027 Abandoned US20110312568A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis, incubation and tandem nucleic acid amplification
US13150177 Abandoned US20110312602A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with thermal bend actuated surface tension valve
US13150241 Abandoned US20110312813A1 (en) 2010-06-17 2011-06-01 Single-use genetic test module
US13150216 Abandoned US20110312608A1 (en) 2010-06-17 2011-06-01 Test module with low-volume hybridization chamber and low-volume reagent reservoir
US13149962 Abandoned US20110312666A1 (en) 2010-06-17 2011-06-01 Microfluidic device with triggered photodetection of fluorescing probe-target hybrid
US13150176 Abandoned US20110312847A1 (en) 2010-06-17 2011-06-01 Spotting device with stored oligonucleotide specification data
US13150159 Abandoned US20110312775A1 (en) 2010-06-17 2011-06-01 Microfluidic device with digital memory
US13150119 Abandoned US20110312763A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with in-loc storage of all required reagents
US13150235 Abandoned US20110312807A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with a membrane seal to prevent dehumidification of the mixture
US13149989 Abandoned US20110312684A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, lysis and nucleic acid amplification
US13150141 Abandoned US20110312082A1 (en) 2010-06-17 2011-06-01 Dispensing apparatus for wafer-scale dispensing of reagents
US13149967 Abandoned US20110312554A1 (en) 2010-06-17 2011-06-01 Microfluidic device with dialysis device, loc and interconnecting cap
US13150205 Abandoned US20110311407A1 (en) 2010-06-17 2011-06-01 Microfluidic boiling-initiated valve
US13150237 Abandoned US20110312809A1 (en) 2010-06-17 2011-06-01 Test module with humidifier
US13150251 Abandoned US20110312822A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device for electrochemiluminescent detection of target nucleic acid sequences
US13149909 Abandoned US20110312633A1 (en) 2010-06-17 2011-06-01 Microfluidic device with dialysis section
US13149952 Abandoned US20110312657A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a mobile telephone
US13150008 Abandoned US20110312539A1 (en) 2010-06-17 2011-06-01 Loc device with electrochemiluminescent probes for detecting targets in a fluid and a positive control probe without a quencher for luminophore emissions
US13150031 Abandoned US20110312070A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr chamber for high rate of temperature change
US13150044 Abandoned US20110312573A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with chemical lysis, incubation and parallel nucleic acid amplification
US13150064 Expired - Fee Related US8398940B2 (en) 2010-06-17 2011-06-01 USB-interfaceable portable test module for electrochemiluminescent detection of targets
US13150144 Abandoned US20110312592A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubation chamber between supporting substrate and heater
US13150232 Abandoned US20110312621A1 (en) 2010-06-17 2011-06-01 Apparatus for dispensing reagents and loading oligonucleotide spotting devices
US13149960 Abandoned US20110312553A1 (en) 2010-06-17 2011-06-01 Microfluidic device with non-imaging optics for electrochemiluminescent detection of targets
US13149984 Abandoned US20110312682A1 (en) 2010-06-17 2011-06-01 Loc device for amplifying and detecting target nucleic acid sequences using electrochemiluminescent resonant energy transfer, stem-and-loop probes with covalently attached primers
US13150002 Abandoned US20110312692A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis and nucleic acid amplification
US13150052 Abandoned US20110312574A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection, genetic analysis and proteomic analysis with dialysis, chemical lysis, incubation and parallel nucleic acid amplification
US13150088 Abandoned US20110312739A1 (en) 2010-06-17 2011-06-01 Single-use test module for pcr amplification of targets and electrochemiluminescent detection of targets
US13149925 Abandoned US20120052562A1 (en) 2010-06-17 2011-06-01 Test module with microfluidic device having laminar structure and sample receptacle
US13149958 Abandoned US20110312663A1 (en) 2010-06-17 2011-06-01 Microfluidic device with time delayed detection of fluorescence from hybridized probes
US13149981 Abandoned US20110312680A1 (en) 2010-06-17 2011-06-01 Loc device for detecting hybridization of target nucleic acid sequences with electrochemiluminescent resonant energy transfer, primer-linked, linear probes
US13150148 Abandoned US20110312843A1 (en) 2010-06-17 2011-06-01 Spotting device for complete assay spotting of locs
US13150187 Abandoned US20110312605A1 (en) 2010-06-17 2011-06-01 Loc device with integral controller
US13150208 Abandoned US20110312852A1 (en) 2010-06-17 2011-06-01 Robotic system for loading oligonucleotides into spotting devices
US13150236 Abandoned US20110312808A1 (en) 2010-06-17 2011-06-01 Test module with controlled exposure of fluorophores to excitation light source
US13150011 Abandoned US20110312695A1 (en) 2010-06-17 2011-06-01 Loc device with hybridization chamber array with positive control chamber containing electrochemiluminescent reporter
US13150006 Abandoned US20110312538A1 (en) 2010-06-17 2011-06-01 Loc device with electrochemiluminescent probes for detecting targets in a fluid and a positive control probe for detecting a nucleic acid sequence known to be present
US13150181 Abandoned US20110312786A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with calibration chamber containing probe designed to be noncomplementary to nucleic acid sequences in the amplicon
US13150222 Abandoned US20110311415A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with thermal bend-actuator surface tension valve
US13150051 Abandoned US20110312714A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for amplification of nucleic acids using dna polymerases of thermophiles
US13150139 Abandoned US20110312590A1 (en) 2010-06-17 2011-06-01 Microfluidic device with elongate incubation chamber
US13150242 Abandoned US20110308313A1 (en) 2010-06-17 2011-06-01 Humidity sensor
US13150089 Abandoned US20110312740A1 (en) 2010-06-17 2011-06-01 Microfluidic device with capillary meniscus marching velocity sensor
US13150189 Abandoned US20110312618A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with high spotting rate
US13150268 Abandoned US20110312837A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis and electrochemiluminescent detection of target sequences
US13149892 Abandoned US20110312623A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis, nucleic acid amplification and prehybridization filtering
US13149920 Abandoned US20110312639A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for separating leukocytes and pathogens from blood
US13149930 Abandoned US20110312552A1 (en) 2010-06-17 2011-06-01 Microfluidic device with conductivity sensor
US13150155 Abandoned US20110312774A1 (en) 2010-06-17 2011-06-01 Microfluidic device for diffusive mixing in small cross sectional area microchannel
US13149941 Abandoned US20110312649A1 (en) 2010-06-17 2011-06-01 Microfluidic device with optically transparent hybridization chambers
US13150191 Abandoned US20110312606A1 (en) 2010-06-17 2011-06-01 Loc device with digital memory
US13149931 Abandoned US20110312641A1 (en) 2010-06-17 2011-06-01 Microfluidic device with sample inlet and probe hybridization section
US13150096 Abandoned US20110312616A1 (en) 2010-06-17 2011-06-01 Test module with parallel dna and rna amplification sections
US13150203 Abandoned US20110312619A1 (en) 2010-06-17 2011-06-01 Device for high-density deposition of biochemicals
US13149924 Abandoned US20110312551A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis which performs nucleic acid amplification before removing non-nucleic acid constituents in a dialysis section
US13149993 Abandoned US20110312686A1 (en) 2010-06-17 2011-06-01 Microfluidic device with elongate pcr chambers
US13150020 Abandoned US20110312564A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis, incubation and nucleic acid amplification
US13150062 Abandoned US20110312723A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using nucleic acid sequence based amplification
US13150075 Abandoned US20110312731A1 (en) 2010-06-17 2011-06-01 Microfluidic device with large angle of collection of emission light
US13150076 Abandoned US20110312581A1 (en) 2010-06-17 2011-06-01 Microfluidic device with nucleic acid amplification chamber heater bonded to chamber interior
US13150140 Abandoned US20110311393A1 (en) 2010-06-17 2011-06-01 Microfluidic device with thermal bend actuated pressure pulse valve
US13150246 Abandoned US20110312817A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with humidity sensor
US13150259 Abandoned US20110312829A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis and electrochemiluminescent detection of target sequences
US13150272 Abandoned US20110308945A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device with thick electrodes for electrochemiluminescent detection of target sequences
US13149921 Abandoned US20110312550A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis which performs nucleic acid amplification after sample preparation in a dialysis section
US13150046 Abandoned US20110312709A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using electrochemiluminescent probes and calibration probes with detection photosensors and calibration photosensors
US13150067 Abandoned US20110312727A1 (en) 2010-06-17 2011-06-01 Loc device with parallel nucleic acid amplification functionality
US13150174 Abandoned US20110312783A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with negative control comprising empty chambers
US13150266 Abandoned US20110312835A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device with electrochemiluminescent probes and integrated photosensor for detection of target sequences
US13149963 Abandoned US20110312667A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a desktop computer
US13150221 Abandoned US20120004145A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting robot for wafer-scale spotting of locs
US13150149 Abandoned US20110312594A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization probes including positive and negative control probes
US13150258 Abandoned US20110312828A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection using electrode pairs optically coupled to photodiode
US13150212 Abandoned US20110312853A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting robot
US13149918 Abandoned US20110312638A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with dialysis and nucleic acid amplification
US13150023 Abandoned US20110312566A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis, incubation and parallel nucleic acid amplification
US13150057 Expired - Fee Related US8383065B2 (en) 2010-06-17 2011-06-01 Test module with integral photosensor for electrochemiluminescent detection of hybridization
US13150098 Abandoned US20110312745A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with photosensor
US13150154 Abandoned US20110312596A1 (en) 2010-06-17 2011-06-01 Microfluidic device with surface tension valve at reagent reservoir outlet
US13150162 Abandoned US20110312598A1 (en) 2010-06-17 2011-06-01 Microfluidic device with reagent mixing proportions determined by outlet valve numbers
US13149934 Abandoned US20110312644A1 (en) 2010-06-17 2011-06-01 Microfluidic device for simultaneous detection of multiple conditions in a patient
US13150102 Abandoned US20110312748A1 (en) 2010-06-17 2011-06-01 Loc with integral photosensor for detection of hybridization assay results
US13150115 Abandoned US20110312759A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with reagent reservoir
US13150153 Abandoned US20120028842A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with positive control chambers incorporating probes that hybridize for any amplicon
US13150248 Abandoned US20110312819A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using electrochemiluminescence of a luminophore in the presence of an electrochemical coreactant
US13149895 Abandoned US20110312625A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis and tandem nucleic acid amplification
US13150003 Abandoned US20110312693A1 (en) 2010-06-17 2011-06-01 Microfluidic device with feedback controlled pcr section
US13150032 Abandoned US20110312702A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis and nucleic acid amplification
US13150250 Abandoned US20110312821A1 (en) 2010-06-17 2011-06-01 Microfluidic device with waste storage
US13149944 Abandoned US20110312651A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low mass probe spots
US13150045 Abandoned US20110312708A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for isothermal amplification of nucleic acids
US13150061 Expired - Fee Related US8388910B2 (en) 2010-06-17 2011-06-01 Portable test module for excitation of electrochemiluminescent probes
US13150083 Abandoned US20110312736A1 (en) 2010-06-17 2011-06-01 Microfluidic device with flow rate sensor
US13150041 Abandoned US20110312706A1 (en) 2010-06-17 2011-06-01 Loc device with hybridization chambers containing probes for electrochemiluminescent detection of target nucleic acid sequences in a fluid and calibration chamber containing probes sealed from the fluid
US13150099 Abandoned US20110312746A1 (en) 2010-06-17 2011-06-01 Microfluidic device with chemical lysis section
US13150165 Abandoned US20110312778A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with negative control chambers incorporating probes designed to be noncomplementary to nucleic acid sequences in the amplicon
US13150178 Abandoned US20110312784A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detecting targets with probes, detection photodiodes and a calibration photodiode
US13149906 Abandoned US20110312631A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with non-specific nucleic acid amplification section and subsequent specific amplification of particular sequences in a separate section
US13150080 Abandoned US20110312734A1 (en) 2010-06-17 2011-06-01 Test module with suspended electrochemiluminescent probes
US13150086 Abandoned US20110312738A1 (en) 2010-06-17 2011-06-01 Microfluidic device with liquid sensor
US13150101 Abandoned US20110312747A1 (en) 2010-06-17 2011-06-01 Microfluidic device for biochemical processing and analysis
US13150122 Abandoned US20110312587A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with primer-linked stem-and-loop probes
US13149936 Abandoned US20110312646A1 (en) 2010-06-17 2011-06-01 Loc device for separating constituents of intermediate size from larger and smaller constituents in a biological sample
US13150168 Abandoned US20110312779A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device for operation under external microprocessor control
US13150261 Abandoned US20110312612A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target sequences with probes between a working electrode and a photosensor
US13150133 Abandoned US20110311409A1 (en) 2010-06-17 2011-06-01 Reagent dispensing apparatus with automatic collection and storage of reagent data
US13150175 Abandoned US20110312601A1 (en) 2010-06-17 2011-06-01 Loc device with digital memory for secure storage of data
US13150021 Abandoned US20110312565A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using hybridization chamber array and negative control chamber containing probes without electrochemiluminescent reporter
US13150158 Abandoned US20110311395A1 (en) 2010-06-17 2011-06-01 Microfluidic device with active valve at reagent reservoir outlet
US13149939 Abandoned US20110312648A1 (en) 2010-06-17 2011-06-01 Microfluidic device for genetic and mitochondrial analysis of a biological sample
US13150065 Abandoned US20110312726A1 (en) 2010-06-17 2011-06-01 Microfluidic device with controllable shunts inside integrated photodiodes
US13150077 Abandoned US20110312732A1 (en) 2010-06-17 2011-06-01 Test module using lanthanide metal-ligand complex, electrochemiluminescent luminophores
US13150090 Abandoned US20110312583A1 (en) 2010-06-17 2011-06-01 Test module with parallel nucleic acid amplification sections
US13150107 Abandoned US20110312586A1 (en) 2010-06-17 2011-06-01 Microfluidic device for chemically and thermally lysing cells
US13149943 Abandoned US20110312076A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with flexible membrane for internal microenvironment pressure-relief
US13149972 Abandoned US20110312675A1 (en) 2010-06-17 2011-06-01 Dialysis device with flow-channel structure for capillary-driven fluidic propulsion without trapped air bubbles
US13150056 Abandoned US20110312718A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using recombinase polymerase amplification
US13150091 Abandoned US20110312584A1 (en) 2010-06-17 2011-06-01 Single-use test module with driver for excitation of electrochemiluminescent luminophores
US13150123 Abandoned US20110312765A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with low oligonucleotide probe mass and low reagent volume
US13150185 Abandoned US20110312787A1 (en) 2010-06-17 2011-06-01 Loc having usb device driver for use in a test module to control usb connection
US13149986 Abandoned US20110312537A1 (en) 2010-06-17 2011-06-01 Loc device for amplifying and detecting target nucleic acid sequences using electrochemiluminescent resonant energy transfer, linear probes with covalently attached primers
US13150183 Abandoned US20110312848A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device for wafer-scale spotting of locs
US13150192 Abandoned US20110312607A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with calibration photosensor output subtracted in a differential circuit from the output of hybridization photosensors
US13149985 Abandoned US20110312683A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with tablet computer
US13150130 Abandoned US20110312768A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with pcr amplification using primers covalently attached to stem-and-loop probes
US13150167 Abandoned US20110312599A1 (en) 2010-06-17 2011-06-01 Microfluidic device with a pcr section with single activation, outlet valve
US13150193 Abandoned US20110312789A1 (en) 2010-06-17 2011-06-01 Loc device with flash memory
US13150108 Abandoned US20110312752A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume reagent reservoir
US13150136 Abandoned US20110312771A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pwm controlled incubation section
US13150226 Abandoned US20110312620A1 (en) 2010-06-17 2011-06-01 System for variable microarray spotting and genetic analysis
US13149914 Abandoned US20110312636A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for separating leukocytes from blood
US13150111 Abandoned US20110312755A1 (en) 2010-06-17 2011-06-01 Test module with chemical lysis section
US13150209 Abandoned US20110309275A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly
US13149897 Abandoned US20110312626A1 (en) 2010-06-17 2011-06-01 Test module incorporating spectrometer
US13150069 Abandoned US20110312578A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for non-specific nucleic acid amplification prior to specific amplification of particular sequences
US13150161 Abandoned US20110312776A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with positive control chambers incorporating reporters
US13150040 Abandoned US20110312705A1 (en) 2010-06-17 2011-06-01 Test module for pcr amplification using low pcr mixture volume
US13150143 Abandoned US20110312842A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device
US13150025 Abandoned US20110312700A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pwm controlled pcr heater
US13150219 Abandoned US20110311414A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with thermal bend-actuator pressure pulse valve
US13150127 Abandoned US20120053088A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for biochemical processing and analysis
US13150194 Abandoned US20110312850A1 (en) 2010-06-17 2011-06-01 Biochemical deposition device with high deposition rate
US13150121 Abandoned US20110312764A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubator
US13149899 Abandoned US20110312546A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with chemical lysis, incubation and tandem nucleic acid amplification
US13149973 Abandoned US20110312676A1 (en) 2010-06-17 2011-06-01 Loc device with integral driver for excitation of electrochemiluminescent luminophores
US13150092 Abandoned US20110312585A1 (en) 2010-06-17 2011-06-01 Microfluidic device with parallel dna and rna amplification section
US13150147 Abandoned US20110312593A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubator having two-dimensional control of input heat flux
US13150218 Abandoned US20110312609A1 (en) 2010-06-17 2011-06-01 Test module for orientation-independent operation
US13150255 Abandoned US20110312825A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection with electrode pairs having complementary and mutually interdigitated finger formations
US13149903 Abandoned US20110312547A1 (en) 2010-06-17 2011-06-01 Microfluidic device with reagent mixing proportions determined by number of active outlet valves
US13149966 Abandoned US20110312670A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with an ebook reader
US13150207 Abandoned US20110312797A1 (en) 2010-06-17 2011-06-01 Portable test module for fluorescence excitation of probe nucleic acid sequences
US13150210 Abandoned US20110312798A1 (en) 2010-06-17 2011-06-01 Test module with inbuilt lancet
US13150265 Abandoned US20110312834A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection using a ruthenium organic complex
US13149911 Abandoned US20110312634A1 (en) 2010-06-17 2011-06-01 Microfluidic device with laminar structure
US13150009 Abandoned US20110312560A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis and tandem nucleic acid amplification
US13150039 Abandoned US20110312572A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with chemical lysis, incubation and nucleic acid amplification
US13150078 Abandoned US20110312526A1 (en) 2010-06-17 2011-06-01 Method of analysing the nucleic acid content of a blood sample
US13150104 Abandoned US20110312749A1 (en) 2010-06-17 2011-06-01 Microfluidic device with thermal lysis section
US13150114 Abandoned US20110312758A1 (en) 2010-06-17 2011-06-01 Test module with thermal lysis section
US13150157 Abandoned US20110312597A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with positive control chambers incorporating probes with no quenchers
US13150173 Abandoned US20110312600A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with thermal bend actuated pressure pulse valve
US13150199 Abandoned US20110312851A1 (en) 2010-06-17 2011-06-01 Device for high density spotting of oligonucleotides
US13149907 Abandoned US20110312632A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr section and diffusion mixer
US13149996 Abandoned US20110312688A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr chamber between supporting substrate and heater
US13150120 Abandoned US20110311418A1 (en) 2010-06-17 2011-06-01 Microvial with digital memory for storage of reagent specification data
US13150128 Abandoned US20110312767A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubation section having temperature feedback
US13150220 Abandoned US20110312610A1 (en) 2010-06-17 2011-06-01 Test module with long fluorescence lifetime probes
US13149956 Abandoned US20110312661A1 (en) 2010-06-17 2011-06-01 Microfluidic device with array of chambers and corresponding diffusion barriers for electrochemiluminescent detection of targets
US13150125 Abandoned US20110312069A1 (en) 2010-06-17 2011-06-01 Microvial with digital memory for storage of oligonucleotide specification data
US13150270 Abandoned US20110312839A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device for electrochemiluminescent detection of target sequences with working electrode in contact with photosensor
US13149990 Abandoned US20110312685A1 (en) 2010-06-17 2011-06-01 Loc device for pcr using adaptor primers and target detection using electrochemiluminescent resonant energy transfer probes
US13150146 Abandoned US20110311394A1 (en) 2010-06-17 2011-06-01 Microfluidic device with thermal bend actuated surface tension valve
US13150217 Abandoned US20110312854A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting robot for spotting arrays of locs
US13149955 Abandoned US20110312660A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a laptop computer
US13150014 Abandoned US20110312561A1 (en) 2010-06-17 2011-06-01 Microfluidic device with photodiodes with controllable shunts to detect fluorescing hybridized probes
US13150214 Abandoned US20110311413A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with liquid detector sensor feedback
US13149947 Abandoned US20110312653A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume hybridization chambers
US13149997 Abandoned US20110312558A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, lysis and tandem nucleic acid amplification
US13150028 Abandoned US20110312569A1 (en) 2010-06-17 2011-06-01 Microfluidic device with small cross sectional area microchannel
US13150050 Expired - Fee Related US8398939B2 (en) 2010-06-17 2011-06-01 Microfluidic test module with low-volume hybridization chambers for electrochemiluminescent detection of target nucleic acid sequences in a fluid
US13150201 Expired - Fee Related US8398938B2 (en) 2010-06-17 2011-06-01 Microfluidic thermal bend actuated pressure pulse valve
US13149891 Abandoned US20110312841A1 (en) 2010-06-17 2011-06-01 Fabrication system for lab-on-a-chip (loc) devices with differing application specific functionality
US13150024 Abandoned US20110312567A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target nucleic acid sequences using hybridization chamber array and negative control chamber without probes
US13150223 Abandoned US20110312611A1 (en) 2010-06-17 2011-06-01 Test module with transition metal-ligand complex fluorophore
US13149913 Abandoned US20110312071A1 (en) 2010-06-17 2011-06-01 Microfluidic device with large channels for cell transport and small channels suitable for biochemical processes
US13149933 Abandoned US20110312643A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of hybridization of nucleic acid targets
US13150134 Abandoned US20110312770A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with nucleic acid amplification using primers covalently attached to linear probes
US13150228 Abandoned US20110312802A1 (en) 2010-06-17 2011-06-01 Test module with probes suspended in fluid
US13149957 Abandoned US20110312662A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for removing cell debris from a biological sample
US13150054 Abandoned US20110312716A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using an isothermal reaction
US13150132 Expired - Fee Related US8394339B2 (en) 2010-06-17 2011-06-01 LOC device with on-chip semiconductor controlled incubation section
US13150244 Abandoned US20110312815A1 (en) 2010-06-17 2011-06-01 Microfluidic device with humidity sensor
US13150179 Abandoned US20110312603A1 (en) 2010-06-17 2011-06-01 Test module with loc having on-chip electronics for module control
US13150225 Abandoned US20110312801A1 (en) 2010-06-17 2011-06-01 Test module with lanthanide metal-ligand complex fluorophore
US13150238 Abandoned US20110312810A1 (en) 2010-06-17 2011-06-01 Single-use test module for detection of hybridization of targets with oligonucleotide probes
US13150263 Abandoned US20110312832A1 (en) 2010-06-17 2011-06-01 Loc device for detection of target sequences with electrochemiluminescent probes in hybridization chambers
US13149902 Abandoned US20110312629A1 (en) 2010-06-17 2011-06-01 Microfluidic device with dialysis section having stomata tapering counter to flow direction
US13150048 Abandoned US20110312711A1 (en) 2010-06-17 2011-06-01 Microfluidic device with controllable shunts peripheral to integrated photodiodes
US13150072 Abandoned US20110312580A1 (en) 2010-06-17 2011-06-01 Loc device with nucleic acid amplification section and thermal insulation trench
US13150074 Abandoned US20110312730A1 (en) 2010-06-17 2011-06-01 Loc device with parallel dna and rna amplification functionality
US13150172 Abandoned US20110312782A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with digital memory
US13149964 Abandoned US20110312668A1 (en) 2010-06-17 2011-06-01 Loc with dialysis section for retaining insoluble sample constituents after amplification and passing soluble constituents to a detection section
US13149991 Abandoned US20110312556A1 (en) 2010-06-17 2011-06-01 Microfluidic device with trigger photodiode in each hybridization chamber
US13149999 Abandoned US20110312689A1 (en) 2010-06-17 2011-06-01 Microfluidic device with sensor-triggered photodetection of fluorescent probe-target hybrid
US13150211 Abandoned US20110312799A1 (en) 2010-06-17 2011-06-01 Usb-interfaceable portable test module for detection of hybridized probes
US13150033 Abandoned US20110312077A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target nucleic acid sequences in a fluid with calibration chamber containing probes designed to be non-complementary with any nucleic acid sequences in the fluid
US13150163 Abandoned US20110312777A1 (en) 2010-06-17 2011-06-01 Test module with digital memory
US13150213 Abandoned US20110312800A1 (en) 2010-06-17 2011-06-01 Test module for gravity-independent operation
US13150234 Abandoned US20110312856A1 (en) 2010-06-17 2011-06-01 Apparatus for dispensing reagents, loading oligonucleotide spotting devices and spotting oligonucleotide probes
US13150252 Abandoned US20110312823A1 (en) 2010-06-17 2011-06-01 Test module with excitation light and mirrors for simultaneous excitation of oligonucleoutide probes
US13149932 Abandoned US20110312642A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of nucleic acid targets with electrochemiluminescent probes
US13150000 Abandoned US20110312690A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr section having two-dimensional control of input heat flux density
US13150042 Abandoned US20110312707A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for pcr amplification of nucleic acids
US13150063 Abandoned US20110312724A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with incubation, nucleic acid amplification and prehybridization filtering
US13150085 Abandoned US20110312582A1 (en) 2010-06-17 2011-06-01 Test module with nucleic acid amplification section
US13150206 Abandoned US20110312796A1 (en) 2010-06-17 2011-06-01 Test module that updates medical databases
US13150016 Abandoned US20110312562A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, chemical lysis and parallel nucleic acid amplification
US13150066 Abandoned US20110312576A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device for multi-stage amplification of nucleic acid sequences
US13150068 Abandoned US20110312577A1 (en) 2010-06-17 2011-06-01 Test module with low-volume hybridization chambers and reagent reservoir for electrochemiluminescent detection of target nucleic acid sequences
US13150018 Abandoned US20110312697A1 (en) 2010-06-17 2011-06-01 Microfluidic device with temperature feedback controlled pcr section
US13150239 Abandoned US20110312811A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target sequences with electrodes profiled for greater peripheral edge length
US13149937 Abandoned US20110312647A1 (en) 2010-06-17 2011-06-01 Microfluidic device with temperature feedback controlled hybridization chambers
US13149969 Abandoned US20110312672A1 (en) 2010-06-17 2011-06-01 Microfluidic assembly with test module and detachable indicator module
US13150017 Abandoned US20110312563A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences in a fluid using hybridization chamber array and negative control chamber containing electrochemiluminescent probe designed to be non-complementary to any sequence in the fluid
US13150047 Abandoned US20110312710A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection, genetic analysis and proteomic analysis with dialysis, chemical lysis, incubation and nucleic acid amplification
US13150106 Abandoned US20110312751A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of mitochondrial dna via fluorescence modulated by hybridization
US13150116 Abandoned US20110312760A1 (en) 2010-06-17 2011-06-01 Reagent microvial with authentication integrated circuit
US13150229 Abandoned US20110312803A1 (en) 2010-06-17 2011-06-01 System for variable loading of reagents into microfluidic device for genetic analysis
US13150059 Abandoned US20110312575A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using a nicking enzyme and a dna polymerase
US13150135 Expired - Fee Related US8383064B2 (en) 2010-06-17 2011-06-01 Genetic test module with low oligonucleotide probe mass and reagent volumes
US13150100 Abandoned US20110312078A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detecting target nucleic acid sequences in mitochondrial dna
US13150195 Abandoned US20110312790A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with low-volume hybridization chamber
US13149904 Abandoned US20110312630A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection, genetic analysis and proteomic analysis with dialysis, chemical lysis, incubation and tandem nucleic acid amplification
US13150095 Abandoned US20110312743A1 (en) 2010-06-17 2011-06-01 Loc device for detection of target nucleic acid sequences using electrodes configured for electrochemiluminescence of luminophores without a coreactant
US13150188 Abandoned US20110312542A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with calibration chamber containing chamber with a blocked inlet spotted with reporter
US13150204 Abandoned US20110312795A1 (en) 2010-06-17 2011-06-01 Diagnostic test module with a loc with integral photosensor and excitation led for detection of hybridization assay results
US13150227 Abandoned US20110309276A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with thermal boiling-initiated valve
US13149959 Abandoned US20110312664A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a dedicated reader
US13149983 Abandoned US20110312681A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for removing erythrocytes from blood
US13150019 Abandoned US20110312698A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr section having short thermal cycle times
US13150164 Abandoned US20110312846A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with fluidics on both sides of supporting substrate
US13150058 Abandoned US20110312720A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis and nucleic acid amplification
US13150253 Abandoned US20110312824A1 (en) 2010-06-17 2011-06-01 Test module with waste storage incorporating porous element
US13150053 Expired - Fee Related US8394340B2 (en) 2010-06-17 2011-06-01 Microfluidic test module with low mass electrochemiluminescent probe spots
US13150084 Abandoned US20110312737A1 (en) 2010-06-17 2011-06-01 Single-use test module for electrochemiluminescent detection of targets
US13149910 Abandoned US20110312549A1 (en) 2010-06-17 2011-06-01 Microfluidic device with multi-layer dialysis section
US13149946 Abandoned US20110312652A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume electrochemiluminescence-based probe spots
US13150070 Abandoned US20110312579A1 (en) 2010-06-17 2011-06-01 Loc device with parallel incubation and parallel nucleic acid amplification functionality
US13150129 Abandoned US20110311408A1 (en) 2010-06-17 2011-06-01 Reagent dispensing apparatus
US13150182 Abandoned US20110312604A1 (en) 2010-06-17 2011-06-01 Loc having on-chip electronics for use in a test module to control module communications
US13150037 Abandoned US20110312704A1 (en) 2010-06-17 2011-06-01 Microfluidic device for pcr amplification using low pcr mixture volume
US13150038 Abandoned US20110312540A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using electrochemiluminescent probes and calibration probes lacking a luminophore
US13150197 Abandoned US20110312792A1 (en) 2010-06-17 2011-06-01 Test module that updates epidemiological databases
US13149908 Abandoned US20110312548A1 (en) 2010-06-17 2011-06-01 Test module with diffusive mixing in small cross sectional area microchannel
US13149935 Abandoned US20110312645A1 (en) 2010-06-17 2011-06-01 Microfluidic device with temperature feedback controlled hybridization chambers for electrochemiluminescent detection of targets
US13149979 Abandoned US20110312555A1 (en) 2010-06-17 2011-06-01 Loc device for detecting hybridization of target nucleic acid sequences with electrochemiluminescent resonant energy transfer, primer-linked, stem-and-loop probes
US13150029 Abandoned US20110312570A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detecting target nucleic acid sequences with probes having long fluorescence lifetime fluorophores
US13150030 Abandoned US20110312701A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target nucleic acid sequences with calibrated photodetection of probes in hybridization array
US13150049 Abandoned US20110312712A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for pcr amplification of nucleic acids from whole blood
US13150093 Abandoned US20110312741A1 (en) 2010-06-17 2011-06-01 Microfluidic device for analysis of mitochondrial dna
US13150137 Abandoned US20110312081A1 (en) 2010-06-17 2011-06-01 Reagent dispensing apparatus for array of microfluidic devices
US13150196 Abandoned US20110312791A1 (en) 2010-06-17 2011-06-01 Test module with fault-tolerant multiple valve assembly
US13150202 Abandoned US20110312794A1 (en) 2010-06-17 2011-06-01 Test module that updates epidemiological databases with location data
US13149894 Pending US20110312624A1 (en) 2010-06-17 2011-06-01 Microfluidic device with flow-channel structure having active valve for capillary-driven fluidic propulsion without trapped air bubbles
US13149927 Abandoned US20110312075A1 (en) 2010-06-17 2011-06-01 Loc device with parallel incubation and parallel dna and rna amplification functionality
US13149950 Abandoned US20110312655A1 (en) 2010-06-17 2011-06-01 Microfluidic device for pcr, probe hybridization and electrochemiluminescent detection of probe-target hybrids
US13150105 Abandoned US20110312750A1 (en) 2010-06-17 2011-06-01 Microfluidic device with total reagent storage
US13150151 Abandoned US20110312595A1 (en) 2010-06-17 2011-06-01 Microfluidic device with mixing section
US13150231 Abandoned US20110312805A1 (en) 2010-06-17 2011-06-01 Test module with time delayed detection of fluorescence from hybridized probe
US13150243 Abandoned US20110312814A1 (en) 2010-06-17 2011-06-01 Single-use test module with excitation source
US13150087 Abandoned US20110312615A1 (en) 2010-06-17 2011-06-01 Microfluidic device with parallel nucleic acid amplification section
US13150190 Abandoned US20110312788A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with thermal boiling-initiated valve
US13150094 Abandoned US20110312742A1 (en) 2010-06-17 2011-06-01 Single-use microfluidic device
US13150118 Abandoned US20110312762A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with fluorescence resonance energy transfer (fret) probes
US13150260 Abandoned US20110312830A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device with electrochemiluminescent probes having a functional moiety for quenching photon emissions configured to change proximity to a luminophore upon forming a probe-target hybrid
US13150267 Abandoned US20110312836A1 (en) 2010-06-17 2011-06-01 Microfluidic device for electrochemiluminescent detection of target sequences
US13149922 Abandoned US20110312074A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with sample receptacle
US13149971 Abandoned US20110312674A1 (en) 2010-06-17 2011-06-01 Loc device with integral photosensor for electrochemiluminescence based detection of targets
US13150142 Abandoned US20110312591A1 (en) 2010-06-17 2011-06-01 Loc with low-volume hybridization chamber and reagent reservoir for genetic analysis
US13150240 Abandoned US20110312812A1 (en) 2010-06-17 2011-06-01 Genetic test module with feedback-controlled humidifier
US13150245 Abandoned US20110312816A1 (en) 2010-06-17 2011-06-01 Test module with led for simultaneous excitation of oligonucleoutide probes
US13149900 Abandoned US20110312628A1 (en) 2010-06-17 2011-06-01 Microfluidic device with mst layer and overlying cap
US13149942 Abandoned US20110312650A1 (en) 2010-06-17 2011-06-01 Microfluidic device with optically transparent hybridization chambers for electrochemiluminescent detection of targets
US13149954 Abandoned US20110312659A1 (en) 2010-06-17 2011-06-01 Microfluidic device with hybridization chambers and corresponding diffusion barriers
US13149965 Abandoned US20110312669A1 (en) 2010-06-17 2011-06-01 Microfluidic device with electrochemiluminescent probes and photosensor with large angle of collection for probe emittted light
US13149970 Abandoned US20110312673A1 (en) 2010-06-17 2011-06-01 Dialysis device with multi-layer structure
US13150001 Abandoned US20110312691A1 (en) 2010-06-17 2011-06-01 Loc device with electrochemiluminescent probes including positive and negative control probes
US13150060 Abandoned US20110312721A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, incubation, and nucleic acid amplification
US13150180 Abandoned US20110312785A1 (en) 2010-06-17 2011-06-01 Spotting device for spotting fixed array of locs
US13150186 Abandoned US20110312849A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device for ejecting low volume droplets
US13150224 Abandoned US20110312855A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting robot for high density spotting of oligonucleotides
US13150233 Abandoned US20110312806A1 (en) 2010-06-17 2011-06-01 Microfluidic device with humidifier
US13150257 Abandoned US20110312827A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device for detection of target sequences with electrochemiluminescent luminophore and functional moiety for quenching photon emissions
US13149995 Abandoned US20110312687A1 (en) 2010-06-17 2011-06-01 Loc device with low volume hybridization chambers and reagent reservoirs for genetic analysis using electrochemiluminescent target detection
US13150150 Abandoned US20110312773A1 (en) 2010-06-17 2011-06-01 Microfluidic device with fault-tolerant multiple valve assembly
US13150256 Abandoned US20110312826A1 (en) 2010-06-17 2011-06-01 Test module with laser for excitation of oligonucleoutide probes
US13149978 Abandoned US20110312678A1 (en) 2010-06-17 2011-06-01 Test module with microfluidic device having dialysis device, loc and interconnecting cap
US13149992 Abandoned US20110312557A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, lysis and parallel nucleic acid amplification
US13150012 Abandoned US20110312696A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, chemical lysis and nucleic acid amplification
US13150071 Abandoned US20110312728A1 (en) 2010-06-17 2011-06-01 Microfluidic device with non-imaging optics
US13150126 Abandoned US20110312541A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with primer-linked linear probes
US13150131 Expired - Fee Related US8354074B2 (en) 2010-06-17 2011-06-01 Test module with low-volume reagent reservoir
US13149974 Abandoned US20110312067A1 (en) 2010-06-17 2011-06-01 Dialysis device for separating pathogens from a biological sample
US13150079 Abandoned US20110312733A1 (en) 2010-06-17 2011-06-01 Loc device with nucleic acid amplification section
US13150081 Abandoned US20110312527A1 (en) 2010-06-17 2011-06-01 Method of analysing the nucleic acid content of biological fluid
US13149961 Abandoned US20110312665A1 (en) 2010-06-17 2011-06-01 Loc with dialysis section for removing insoluble sample constituents from a nucleic acid mixture
US13150117 Abandoned US20110312761A1 (en) 2010-06-17 2011-06-01 Test module for chemically and thermally lysing cells
US13150249 Abandoned US20110312820A1 (en) 2010-06-17 2011-06-01 Test module with excitation light and prisms for simultaneous excitation of oligonucleoutide probes
US13150004 Abandoned US20110312694A1 (en) 2010-06-17 2011-06-01 Microfluidic device with delay-triggered photodetection of fluorescent probe-target hybrid
US13150073 Abandoned US20110312729A1 (en) 2010-06-17 2011-06-01 Test module using transition metal-ligand complex, electrochemiluminescent luminophores
US13149898 Expired - Fee Related US8349277B2 (en) 2010-06-17 2011-06-01 Test module with microfluidic device having LOC and dialysis device for separating pathogens from other constituents in a biological sample
US13149928 Abandoned US20110312640A1 (en) 2010-06-17 2011-06-01 Microfluidic device with photosensor
US13149968 Abandoned US20110312671A1 (en) 2010-06-17 2011-06-01 Single use microfluidic device with photosensor for electrochemiluminescent detection of targets
US13149976 Abandoned US20110312068A1 (en) 2010-06-17 2011-06-01 Dialysis device for separating nucleated cells in a biological sample from other constituents
US13150022 Abandoned US20110312699A1 (en) 2010-06-17 2011-06-01 Microfluidic device with on-chip semiconductor controlled pcr section
US13150113 Abandoned US20110312757A1 (en) 2010-06-17 2011-06-01 Reagent microvial with digital memory
US13150156 Abandoned US20110312617A1 (en) 2010-06-17 2011-06-01 Monolithic microsystems technology device for oligonucleotide spotting
US13149912 Abandoned US20110312635A1 (en) 2010-06-17 2011-06-01 Microfluidic device with flow-channel structure for capillary-driven fluidic propulsion without trapped air bubbles
US13149975 Abandoned US20110312677A1 (en) 2010-06-17 2011-06-01 Loc device for detection of targets with electrochemiluminescent resonant energy transfer probes
US13150247 Abandoned US20110312818A1 (en) 2010-06-17 2011-06-01 Test module with excitation light and lens for simultaneous excitation of oligonucleoutide probes
US13685105 Abandoned US20130079254A1 (en) 2010-06-17 2012-11-26 Microfluidic dialysis device

Family Applications Before (221)

Application Number Title Priority Date Filing Date
US13149948 Abandoned US20110312654A1 (en) 2010-06-17 2011-06-01 Apparatus for loading oligonucleotide spotting devices and spotting oligonucleotide probes
US13149951 Abandoned US20110312656A1 (en) 2010-06-17 2011-06-01 Microfluidic device for pcr and probe hybridization
US13149890 Abandoned US20110312622A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume hybridization chambers for electrochemiluminescent detection of target sequences
US13150007 Abandoned US20110312559A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis and parallel nucleic acid amplification
US13150082 Abandoned US20110312735A1 (en) 2010-06-17 2011-06-01 Microfluidic device with nucleic acid amplification section
US13150109 Abandoned US20110312753A1 (en) 2010-06-17 2011-06-01 Loc with integral led driver for excitation led
US13150112 Abandoned US20110312756A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low reagent volumes
US13150035 Abandoned US20110312703A1 (en) 2010-06-17 2011-06-01 Microfluidic device for rapid pcr amplification
US13150160 Abandoned US20110312845A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with laminar structure
US13150200 Abandoned US20110312793A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with low mass of probes
US13150269 Abandoned US20110312838A1 (en) 2010-06-17 2011-06-01 Microfluidic device with electrochemiluminescent probes and integrated photosensor for detection of target molecules
US13149893 Abandoned US20110312545A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, chemical lysis and tandem nucleic acid amplification
US13149919 Abandoned US20110312073A1 (en) 2010-06-17 2011-06-01 Microfluidic test module incorporating surface micro-machined chips and interconnecting cap
US13150036 Abandoned US20110312571A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis and parallel nucleic acid amplification
US13150055 Abandoned US20110312717A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, incubation and nucleic acid amplification
US13150170 Abandoned US20110312781A1 (en) 2010-06-17 2011-06-01 Loc with digital memory to store genetic data updates
US13149916 Abandoned US20110312072A1 (en) 2010-06-17 2011-06-01 Microfluidic device with surface micro-machined chips and interconnecting cap
US13150271 Abandoned US20110312840A1 (en) 2010-06-17 2011-06-01 Microfluidic device with sample inlet, electrochemiluminescent probes and integrated photosensor for detection of target sequences
US13149929 Abandoned US20110311411A1 (en) 2010-06-17 2011-06-01 Microfluidic thermal bend actuated surface tension valve
US13150110 Abandoned US20110312754A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of mitochondrial dna via electrochemiluminescence modulated hybridization
US13150152 Abandoned US20110312844A1 (en) 2010-06-17 2011-06-01 Biochemical deposition device
US13150262 Abandoned US20110312831A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequence with electrochemiluminescent metalorganic complex
US13149917 Abandoned US20110312637A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for separating pathogens from a biological sample
US13150097 Abandoned US20110312744A1 (en) 2010-06-17 2011-06-01 Microfluidic device for amplifying mitochondrial dna in a biological sample
US13150230 Abandoned US20110312804A1 (en) 2010-06-17 2011-06-01 Microfluidic device with aperture with geometry to promote unpinned flow-through of fluid
US13150264 Abandoned US20110312833A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target sequences using transparent electrodes
US13149980 Abandoned US20110312679A1 (en) 2010-06-17 2011-06-01 Microfluidic device with surface-micromachined dialysis section
US13150124 Abandoned US20110312766A1 (en) 2010-06-17 2011-06-01 Microfluidic device with feedback controlled incubation section
US13150138 Abandoned US20110312772A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with pcr amplification using linker primers
US13150166 Abandoned US20110312079A1 (en) 2010-06-17 2011-06-01 Loc with digital memory to store epidemiological updates
US13150169 Abandoned US20110312780A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with negative control chambers incorporating probes with no reporters
US13150184 Expired - Fee Related US8425845B2 (en) 2010-06-17 2011-06-01 Genetic analysis LOC with hybridization array with calibration chamber containing probe that lacks a reporter
US13149953 Abandoned US20110312658A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for concentrating nucleated cells in a biological sample
US13150027 Abandoned US20110312568A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis, incubation and tandem nucleic acid amplification
US13150177 Abandoned US20110312602A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with thermal bend actuated surface tension valve
US13150241 Abandoned US20110312813A1 (en) 2010-06-17 2011-06-01 Single-use genetic test module
US13150216 Abandoned US20110312608A1 (en) 2010-06-17 2011-06-01 Test module with low-volume hybridization chamber and low-volume reagent reservoir
US13149962 Abandoned US20110312666A1 (en) 2010-06-17 2011-06-01 Microfluidic device with triggered photodetection of fluorescing probe-target hybrid
US13150176 Abandoned US20110312847A1 (en) 2010-06-17 2011-06-01 Spotting device with stored oligonucleotide specification data
US13150159 Abandoned US20110312775A1 (en) 2010-06-17 2011-06-01 Microfluidic device with digital memory
US13150119 Abandoned US20110312763A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with in-loc storage of all required reagents
US13150235 Abandoned US20110312807A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with a membrane seal to prevent dehumidification of the mixture
US13149989 Abandoned US20110312684A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, lysis and nucleic acid amplification
US13150141 Abandoned US20110312082A1 (en) 2010-06-17 2011-06-01 Dispensing apparatus for wafer-scale dispensing of reagents
US13149967 Abandoned US20110312554A1 (en) 2010-06-17 2011-06-01 Microfluidic device with dialysis device, loc and interconnecting cap
US13150205 Abandoned US20110311407A1 (en) 2010-06-17 2011-06-01 Microfluidic boiling-initiated valve
US13150237 Abandoned US20110312809A1 (en) 2010-06-17 2011-06-01 Test module with humidifier
US13150251 Abandoned US20110312822A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device for electrochemiluminescent detection of target nucleic acid sequences
US13149909 Abandoned US20110312633A1 (en) 2010-06-17 2011-06-01 Microfluidic device with dialysis section
US13149952 Abandoned US20110312657A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a mobile telephone
US13150008 Abandoned US20110312539A1 (en) 2010-06-17 2011-06-01 Loc device with electrochemiluminescent probes for detecting targets in a fluid and a positive control probe without a quencher for luminophore emissions
US13150031 Abandoned US20110312070A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr chamber for high rate of temperature change
US13150044 Abandoned US20110312573A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with chemical lysis, incubation and parallel nucleic acid amplification
US13150064 Expired - Fee Related US8398940B2 (en) 2010-06-17 2011-06-01 USB-interfaceable portable test module for electrochemiluminescent detection of targets
US13150144 Abandoned US20110312592A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubation chamber between supporting substrate and heater
US13150232 Abandoned US20110312621A1 (en) 2010-06-17 2011-06-01 Apparatus for dispensing reagents and loading oligonucleotide spotting devices
US13149960 Abandoned US20110312553A1 (en) 2010-06-17 2011-06-01 Microfluidic device with non-imaging optics for electrochemiluminescent detection of targets
US13149984 Abandoned US20110312682A1 (en) 2010-06-17 2011-06-01 Loc device for amplifying and detecting target nucleic acid sequences using electrochemiluminescent resonant energy transfer, stem-and-loop probes with covalently attached primers
US13150002 Abandoned US20110312692A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis and nucleic acid amplification
US13150052 Abandoned US20110312574A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection, genetic analysis and proteomic analysis with dialysis, chemical lysis, incubation and parallel nucleic acid amplification
US13150088 Abandoned US20110312739A1 (en) 2010-06-17 2011-06-01 Single-use test module for pcr amplification of targets and electrochemiluminescent detection of targets
US13149925 Abandoned US20120052562A1 (en) 2010-06-17 2011-06-01 Test module with microfluidic device having laminar structure and sample receptacle
US13149958 Abandoned US20110312663A1 (en) 2010-06-17 2011-06-01 Microfluidic device with time delayed detection of fluorescence from hybridized probes
US13149981 Abandoned US20110312680A1 (en) 2010-06-17 2011-06-01 Loc device for detecting hybridization of target nucleic acid sequences with electrochemiluminescent resonant energy transfer, primer-linked, linear probes
US13150148 Abandoned US20110312843A1 (en) 2010-06-17 2011-06-01 Spotting device for complete assay spotting of locs
US13150187 Abandoned US20110312605A1 (en) 2010-06-17 2011-06-01 Loc device with integral controller
US13150208 Abandoned US20110312852A1 (en) 2010-06-17 2011-06-01 Robotic system for loading oligonucleotides into spotting devices
US13150236 Abandoned US20110312808A1 (en) 2010-06-17 2011-06-01 Test module with controlled exposure of fluorophores to excitation light source
US13150011 Abandoned US20110312695A1 (en) 2010-06-17 2011-06-01 Loc device with hybridization chamber array with positive control chamber containing electrochemiluminescent reporter
US13150006 Abandoned US20110312538A1 (en) 2010-06-17 2011-06-01 Loc device with electrochemiluminescent probes for detecting targets in a fluid and a positive control probe for detecting a nucleic acid sequence known to be present
US13150181 Abandoned US20110312786A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with calibration chamber containing probe designed to be noncomplementary to nucleic acid sequences in the amplicon
US13150222 Abandoned US20110311415A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with thermal bend-actuator surface tension valve
US13150051 Abandoned US20110312714A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for amplification of nucleic acids using dna polymerases of thermophiles
US13150139 Abandoned US20110312590A1 (en) 2010-06-17 2011-06-01 Microfluidic device with elongate incubation chamber
US13150242 Abandoned US20110308313A1 (en) 2010-06-17 2011-06-01 Humidity sensor
US13150089 Abandoned US20110312740A1 (en) 2010-06-17 2011-06-01 Microfluidic device with capillary meniscus marching velocity sensor
US13150189 Abandoned US20110312618A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with high spotting rate
US13150268 Abandoned US20110312837A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis and electrochemiluminescent detection of target sequences
US13149892 Abandoned US20110312623A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis, nucleic acid amplification and prehybridization filtering
US13149920 Abandoned US20110312639A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for separating leukocytes and pathogens from blood
US13149930 Abandoned US20110312552A1 (en) 2010-06-17 2011-06-01 Microfluidic device with conductivity sensor
US13150155 Abandoned US20110312774A1 (en) 2010-06-17 2011-06-01 Microfluidic device for diffusive mixing in small cross sectional area microchannel
US13149941 Abandoned US20110312649A1 (en) 2010-06-17 2011-06-01 Microfluidic device with optically transparent hybridization chambers
US13150191 Abandoned US20110312606A1 (en) 2010-06-17 2011-06-01 Loc device with digital memory
US13149931 Abandoned US20110312641A1 (en) 2010-06-17 2011-06-01 Microfluidic device with sample inlet and probe hybridization section
US13150096 Abandoned US20110312616A1 (en) 2010-06-17 2011-06-01 Test module with parallel dna and rna amplification sections
US13150203 Abandoned US20110312619A1 (en) 2010-06-17 2011-06-01 Device for high-density deposition of biochemicals
US13149924 Abandoned US20110312551A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis which performs nucleic acid amplification before removing non-nucleic acid constituents in a dialysis section
US13149993 Abandoned US20110312686A1 (en) 2010-06-17 2011-06-01 Microfluidic device with elongate pcr chambers
US13150020 Abandoned US20110312564A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis, incubation and nucleic acid amplification
US13150062 Abandoned US20110312723A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using nucleic acid sequence based amplification
US13150075 Abandoned US20110312731A1 (en) 2010-06-17 2011-06-01 Microfluidic device with large angle of collection of emission light
US13150076 Abandoned US20110312581A1 (en) 2010-06-17 2011-06-01 Microfluidic device with nucleic acid amplification chamber heater bonded to chamber interior
US13150140 Abandoned US20110311393A1 (en) 2010-06-17 2011-06-01 Microfluidic device with thermal bend actuated pressure pulse valve
US13150246 Abandoned US20110312817A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with humidity sensor
US13150259 Abandoned US20110312829A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis and electrochemiluminescent detection of target sequences
US13150272 Abandoned US20110308945A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device with thick electrodes for electrochemiluminescent detection of target sequences
US13149921 Abandoned US20110312550A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis which performs nucleic acid amplification after sample preparation in a dialysis section
US13150046 Abandoned US20110312709A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using electrochemiluminescent probes and calibration probes with detection photosensors and calibration photosensors
US13150067 Abandoned US20110312727A1 (en) 2010-06-17 2011-06-01 Loc device with parallel nucleic acid amplification functionality
US13150174 Abandoned US20110312783A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with negative control comprising empty chambers
US13150266 Abandoned US20110312835A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device with electrochemiluminescent probes and integrated photosensor for detection of target sequences
US13149963 Abandoned US20110312667A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a desktop computer
US13150221 Abandoned US20120004145A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting robot for wafer-scale spotting of locs
US13150149 Abandoned US20110312594A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization probes including positive and negative control probes
US13150258 Abandoned US20110312828A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection using electrode pairs optically coupled to photodiode
US13150212 Abandoned US20110312853A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting robot
US13149918 Abandoned US20110312638A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with dialysis and nucleic acid amplification
US13150023 Abandoned US20110312566A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis, incubation and parallel nucleic acid amplification
US13150057 Expired - Fee Related US8383065B2 (en) 2010-06-17 2011-06-01 Test module with integral photosensor for electrochemiluminescent detection of hybridization
US13150098 Abandoned US20110312745A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with photosensor
US13150154 Abandoned US20110312596A1 (en) 2010-06-17 2011-06-01 Microfluidic device with surface tension valve at reagent reservoir outlet
US13150162 Abandoned US20110312598A1 (en) 2010-06-17 2011-06-01 Microfluidic device with reagent mixing proportions determined by outlet valve numbers
US13149934 Abandoned US20110312644A1 (en) 2010-06-17 2011-06-01 Microfluidic device for simultaneous detection of multiple conditions in a patient
US13150102 Abandoned US20110312748A1 (en) 2010-06-17 2011-06-01 Loc with integral photosensor for detection of hybridization assay results
US13150115 Abandoned US20110312759A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with reagent reservoir
US13150153 Abandoned US20120028842A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with positive control chambers incorporating probes that hybridize for any amplicon
US13150248 Abandoned US20110312819A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using electrochemiluminescence of a luminophore in the presence of an electrochemical coreactant
US13149895 Abandoned US20110312625A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis and tandem nucleic acid amplification
US13150003 Abandoned US20110312693A1 (en) 2010-06-17 2011-06-01 Microfluidic device with feedback controlled pcr section
US13150032 Abandoned US20110312702A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis, chemical lysis and nucleic acid amplification
US13150250 Abandoned US20110312821A1 (en) 2010-06-17 2011-06-01 Microfluidic device with waste storage
US13149944 Abandoned US20110312651A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low mass probe spots
US13150045 Abandoned US20110312708A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for isothermal amplification of nucleic acids
US13150061 Expired - Fee Related US8388910B2 (en) 2010-06-17 2011-06-01 Portable test module for excitation of electrochemiluminescent probes
US13150083 Abandoned US20110312736A1 (en) 2010-06-17 2011-06-01 Microfluidic device with flow rate sensor
US13150041 Abandoned US20110312706A1 (en) 2010-06-17 2011-06-01 Loc device with hybridization chambers containing probes for electrochemiluminescent detection of target nucleic acid sequences in a fluid and calibration chamber containing probes sealed from the fluid
US13150099 Abandoned US20110312746A1 (en) 2010-06-17 2011-06-01 Microfluidic device with chemical lysis section
US13150165 Abandoned US20110312778A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with negative control chambers incorporating probes designed to be noncomplementary to nucleic acid sequences in the amplicon
US13150178 Abandoned US20110312784A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detecting targets with probes, detection photodiodes and a calibration photodiode
US13149906 Abandoned US20110312631A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with non-specific nucleic acid amplification section and subsequent specific amplification of particular sequences in a separate section
US13150080 Abandoned US20110312734A1 (en) 2010-06-17 2011-06-01 Test module with suspended electrochemiluminescent probes
US13150086 Abandoned US20110312738A1 (en) 2010-06-17 2011-06-01 Microfluidic device with liquid sensor
US13150101 Abandoned US20110312747A1 (en) 2010-06-17 2011-06-01 Microfluidic device for biochemical processing and analysis
US13150122 Abandoned US20110312587A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with primer-linked stem-and-loop probes
US13149936 Abandoned US20110312646A1 (en) 2010-06-17 2011-06-01 Loc device for separating constituents of intermediate size from larger and smaller constituents in a biological sample
US13150168 Abandoned US20110312779A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device for operation under external microprocessor control
US13150261 Abandoned US20110312612A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target sequences with probes between a working electrode and a photosensor
US13150133 Abandoned US20110311409A1 (en) 2010-06-17 2011-06-01 Reagent dispensing apparatus with automatic collection and storage of reagent data
US13150175 Abandoned US20110312601A1 (en) 2010-06-17 2011-06-01 Loc device with digital memory for secure storage of data
US13150021 Abandoned US20110312565A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using hybridization chamber array and negative control chamber containing probes without electrochemiluminescent reporter
US13150158 Abandoned US20110311395A1 (en) 2010-06-17 2011-06-01 Microfluidic device with active valve at reagent reservoir outlet
US13149939 Abandoned US20110312648A1 (en) 2010-06-17 2011-06-01 Microfluidic device for genetic and mitochondrial analysis of a biological sample
US13150065 Abandoned US20110312726A1 (en) 2010-06-17 2011-06-01 Microfluidic device with controllable shunts inside integrated photodiodes
US13150077 Abandoned US20110312732A1 (en) 2010-06-17 2011-06-01 Test module using lanthanide metal-ligand complex, electrochemiluminescent luminophores
US13150090 Abandoned US20110312583A1 (en) 2010-06-17 2011-06-01 Test module with parallel nucleic acid amplification sections
US13150107 Abandoned US20110312586A1 (en) 2010-06-17 2011-06-01 Microfluidic device for chemically and thermally lysing cells
US13149943 Abandoned US20110312076A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with flexible membrane for internal microenvironment pressure-relief
US13149972 Abandoned US20110312675A1 (en) 2010-06-17 2011-06-01 Dialysis device with flow-channel structure for capillary-driven fluidic propulsion without trapped air bubbles
US13150056 Abandoned US20110312718A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using recombinase polymerase amplification
US13150091 Abandoned US20110312584A1 (en) 2010-06-17 2011-06-01 Single-use test module with driver for excitation of electrochemiluminescent luminophores
US13150123 Abandoned US20110312765A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with low oligonucleotide probe mass and low reagent volume
US13150185 Abandoned US20110312787A1 (en) 2010-06-17 2011-06-01 Loc having usb device driver for use in a test module to control usb connection
US13149986 Abandoned US20110312537A1 (en) 2010-06-17 2011-06-01 Loc device for amplifying and detecting target nucleic acid sequences using electrochemiluminescent resonant energy transfer, linear probes with covalently attached primers
US13150183 Abandoned US20110312848A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device for wafer-scale spotting of locs
US13150192 Abandoned US20110312607A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with calibration photosensor output subtracted in a differential circuit from the output of hybridization photosensors
US13149985 Abandoned US20110312683A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with tablet computer
US13150130 Abandoned US20110312768A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with pcr amplification using primers covalently attached to stem-and-loop probes
US13150167 Abandoned US20110312599A1 (en) 2010-06-17 2011-06-01 Microfluidic device with a pcr section with single activation, outlet valve
US13150193 Abandoned US20110312789A1 (en) 2010-06-17 2011-06-01 Loc device with flash memory
US13150108 Abandoned US20110312752A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume reagent reservoir
US13150136 Abandoned US20110312771A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pwm controlled incubation section
US13150226 Abandoned US20110312620A1 (en) 2010-06-17 2011-06-01 System for variable microarray spotting and genetic analysis
US13149914 Abandoned US20110312636A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for separating leukocytes from blood
US13150111 Abandoned US20110312755A1 (en) 2010-06-17 2011-06-01 Test module with chemical lysis section
US13150209 Abandoned US20110309275A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly
US13149897 Abandoned US20110312626A1 (en) 2010-06-17 2011-06-01 Test module incorporating spectrometer
US13150069 Abandoned US20110312578A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for non-specific nucleic acid amplification prior to specific amplification of particular sequences
US13150161 Abandoned US20110312776A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with positive control chambers incorporating reporters
US13150040 Abandoned US20110312705A1 (en) 2010-06-17 2011-06-01 Test module for pcr amplification using low pcr mixture volume
US13150143 Abandoned US20110312842A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device
US13150025 Abandoned US20110312700A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pwm controlled pcr heater
US13150219 Abandoned US20110311414A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with thermal bend-actuator pressure pulse valve
US13150127 Abandoned US20120053088A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for biochemical processing and analysis
US13150194 Abandoned US20110312850A1 (en) 2010-06-17 2011-06-01 Biochemical deposition device with high deposition rate
US13150121 Abandoned US20110312764A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubator
US13149899 Abandoned US20110312546A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with chemical lysis, incubation and tandem nucleic acid amplification
US13149973 Abandoned US20110312676A1 (en) 2010-06-17 2011-06-01 Loc device with integral driver for excitation of electrochemiluminescent luminophores
US13150092 Abandoned US20110312585A1 (en) 2010-06-17 2011-06-01 Microfluidic device with parallel dna and rna amplification section
US13150147 Abandoned US20110312593A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubator having two-dimensional control of input heat flux
US13150218 Abandoned US20110312609A1 (en) 2010-06-17 2011-06-01 Test module for orientation-independent operation
US13150255 Abandoned US20110312825A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection with electrode pairs having complementary and mutually interdigitated finger formations
US13149903 Abandoned US20110312547A1 (en) 2010-06-17 2011-06-01 Microfluidic device with reagent mixing proportions determined by number of active outlet valves
US13149966 Abandoned US20110312670A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with an ebook reader
US13150207 Abandoned US20110312797A1 (en) 2010-06-17 2011-06-01 Portable test module for fluorescence excitation of probe nucleic acid sequences
US13150210 Abandoned US20110312798A1 (en) 2010-06-17 2011-06-01 Test module with inbuilt lancet
US13150265 Abandoned US20110312834A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection using a ruthenium organic complex
US13149911 Abandoned US20110312634A1 (en) 2010-06-17 2011-06-01 Microfluidic device with laminar structure
US13150009 Abandoned US20110312560A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, thermal lysis and tandem nucleic acid amplification
US13150039 Abandoned US20110312572A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with chemical lysis, incubation and nucleic acid amplification
US13150078 Abandoned US20110312526A1 (en) 2010-06-17 2011-06-01 Method of analysing the nucleic acid content of a blood sample
US13150104 Abandoned US20110312749A1 (en) 2010-06-17 2011-06-01 Microfluidic device with thermal lysis section
US13150114 Abandoned US20110312758A1 (en) 2010-06-17 2011-06-01 Test module with thermal lysis section
US13150157 Abandoned US20110312597A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with positive control chambers incorporating probes with no quenchers
US13150173 Abandoned US20110312600A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with thermal bend actuated pressure pulse valve
US13150199 Abandoned US20110312851A1 (en) 2010-06-17 2011-06-01 Device for high density spotting of oligonucleotides
US13149907 Abandoned US20110312632A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr section and diffusion mixer
US13149996 Abandoned US20110312688A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr chamber between supporting substrate and heater
US13150120 Abandoned US20110311418A1 (en) 2010-06-17 2011-06-01 Microvial with digital memory for storage of reagent specification data
US13150128 Abandoned US20110312767A1 (en) 2010-06-17 2011-06-01 Microfluidic device with incubation section having temperature feedback
US13150220 Abandoned US20110312610A1 (en) 2010-06-17 2011-06-01 Test module with long fluorescence lifetime probes
US13149956 Abandoned US20110312661A1 (en) 2010-06-17 2011-06-01 Microfluidic device with array of chambers and corresponding diffusion barriers for electrochemiluminescent detection of targets
US13150125 Abandoned US20110312069A1 (en) 2010-06-17 2011-06-01 Microvial with digital memory for storage of oligonucleotide specification data
US13150270 Abandoned US20110312839A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device for electrochemiluminescent detection of target sequences with working electrode in contact with photosensor
US13149990 Abandoned US20110312685A1 (en) 2010-06-17 2011-06-01 Loc device for pcr using adaptor primers and target detection using electrochemiluminescent resonant energy transfer probes
US13150146 Abandoned US20110311394A1 (en) 2010-06-17 2011-06-01 Microfluidic device with thermal bend actuated surface tension valve
US13150217 Abandoned US20110312854A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting robot for spotting arrays of locs
US13149955 Abandoned US20110312660A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a laptop computer
US13150014 Abandoned US20110312561A1 (en) 2010-06-17 2011-06-01 Microfluidic device with photodiodes with controllable shunts to detect fluorescing hybridized probes
US13150214 Abandoned US20110311413A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with liquid detector sensor feedback
US13149947 Abandoned US20110312653A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume hybridization chambers
US13149997 Abandoned US20110312558A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, lysis and tandem nucleic acid amplification
US13150028 Abandoned US20110312569A1 (en) 2010-06-17 2011-06-01 Microfluidic device with small cross sectional area microchannel
US13150050 Expired - Fee Related US8398939B2 (en) 2010-06-17 2011-06-01 Microfluidic test module with low-volume hybridization chambers for electrochemiluminescent detection of target nucleic acid sequences in a fluid
US13150201 Expired - Fee Related US8398938B2 (en) 2010-06-17 2011-06-01 Microfluidic thermal bend actuated pressure pulse valve
US13149891 Abandoned US20110312841A1 (en) 2010-06-17 2011-06-01 Fabrication system for lab-on-a-chip (loc) devices with differing application specific functionality
US13150024 Abandoned US20110312567A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target nucleic acid sequences using hybridization chamber array and negative control chamber without probes
US13150223 Abandoned US20110312611A1 (en) 2010-06-17 2011-06-01 Test module with transition metal-ligand complex fluorophore
US13149913 Abandoned US20110312071A1 (en) 2010-06-17 2011-06-01 Microfluidic device with large channels for cell transport and small channels suitable for biochemical processes
US13149933 Abandoned US20110312643A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of hybridization of nucleic acid targets
US13150134 Abandoned US20110312770A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with nucleic acid amplification using primers covalently attached to linear probes

Family Applications After (133)

Application Number Title Priority Date Filing Date
US13149957 Abandoned US20110312662A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for removing cell debris from a biological sample
US13150054 Abandoned US20110312716A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using an isothermal reaction
US13150132 Expired - Fee Related US8394339B2 (en) 2010-06-17 2011-06-01 LOC device with on-chip semiconductor controlled incubation section
US13150244 Abandoned US20110312815A1 (en) 2010-06-17 2011-06-01 Microfluidic device with humidity sensor
US13150179 Abandoned US20110312603A1 (en) 2010-06-17 2011-06-01 Test module with loc having on-chip electronics for module control
US13150225 Abandoned US20110312801A1 (en) 2010-06-17 2011-06-01 Test module with lanthanide metal-ligand complex fluorophore
US13150238 Abandoned US20110312810A1 (en) 2010-06-17 2011-06-01 Single-use test module for detection of hybridization of targets with oligonucleotide probes
US13150263 Abandoned US20110312832A1 (en) 2010-06-17 2011-06-01 Loc device for detection of target sequences with electrochemiluminescent probes in hybridization chambers
US13149902 Abandoned US20110312629A1 (en) 2010-06-17 2011-06-01 Microfluidic device with dialysis section having stomata tapering counter to flow direction
US13150048 Abandoned US20110312711A1 (en) 2010-06-17 2011-06-01 Microfluidic device with controllable shunts peripheral to integrated photodiodes
US13150072 Abandoned US20110312580A1 (en) 2010-06-17 2011-06-01 Loc device with nucleic acid amplification section and thermal insulation trench
US13150074 Abandoned US20110312730A1 (en) 2010-06-17 2011-06-01 Loc device with parallel dna and rna amplification functionality
US13150172 Abandoned US20110312782A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with digital memory
US13149964 Abandoned US20110312668A1 (en) 2010-06-17 2011-06-01 Loc with dialysis section for retaining insoluble sample constituents after amplification and passing soluble constituents to a detection section
US13149991 Abandoned US20110312556A1 (en) 2010-06-17 2011-06-01 Microfluidic device with trigger photodiode in each hybridization chamber
US13149999 Abandoned US20110312689A1 (en) 2010-06-17 2011-06-01 Microfluidic device with sensor-triggered photodetection of fluorescent probe-target hybrid
US13150211 Abandoned US20110312799A1 (en) 2010-06-17 2011-06-01 Usb-interfaceable portable test module for detection of hybridized probes
US13150033 Abandoned US20110312077A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target nucleic acid sequences in a fluid with calibration chamber containing probes designed to be non-complementary with any nucleic acid sequences in the fluid
US13150163 Abandoned US20110312777A1 (en) 2010-06-17 2011-06-01 Test module with digital memory
US13150213 Abandoned US20110312800A1 (en) 2010-06-17 2011-06-01 Test module for gravity-independent operation
US13150234 Abandoned US20110312856A1 (en) 2010-06-17 2011-06-01 Apparatus for dispensing reagents, loading oligonucleotide spotting devices and spotting oligonucleotide probes
US13150252 Abandoned US20110312823A1 (en) 2010-06-17 2011-06-01 Test module with excitation light and mirrors for simultaneous excitation of oligonucleoutide probes
US13149932 Abandoned US20110312642A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of nucleic acid targets with electrochemiluminescent probes
US13150000 Abandoned US20110312690A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr section having two-dimensional control of input heat flux density
US13150042 Abandoned US20110312707A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for pcr amplification of nucleic acids
US13150063 Abandoned US20110312724A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection and genetic analysis with incubation, nucleic acid amplification and prehybridization filtering
US13150085 Abandoned US20110312582A1 (en) 2010-06-17 2011-06-01 Test module with nucleic acid amplification section
US13150206 Abandoned US20110312796A1 (en) 2010-06-17 2011-06-01 Test module that updates medical databases
US13150016 Abandoned US20110312562A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection with dialysis, chemical lysis and parallel nucleic acid amplification
US13150066 Abandoned US20110312576A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device for multi-stage amplification of nucleic acid sequences
US13150068 Abandoned US20110312577A1 (en) 2010-06-17 2011-06-01 Test module with low-volume hybridization chambers and reagent reservoir for electrochemiluminescent detection of target nucleic acid sequences
US13150018 Abandoned US20110312697A1 (en) 2010-06-17 2011-06-01 Microfluidic device with temperature feedback controlled pcr section
US13150239 Abandoned US20110312811A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target sequences with electrodes profiled for greater peripheral edge length
US13149937 Abandoned US20110312647A1 (en) 2010-06-17 2011-06-01 Microfluidic device with temperature feedback controlled hybridization chambers
US13149969 Abandoned US20110312672A1 (en) 2010-06-17 2011-06-01 Microfluidic assembly with test module and detachable indicator module
US13150017 Abandoned US20110312563A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences in a fluid using hybridization chamber array and negative control chamber containing electrochemiluminescent probe designed to be non-complementary to any sequence in the fluid
US13150047 Abandoned US20110312710A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection, genetic analysis and proteomic analysis with dialysis, chemical lysis, incubation and nucleic acid amplification
US13150106 Abandoned US20110312751A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detection of mitochondrial dna via fluorescence modulated by hybridization
US13150116 Abandoned US20110312760A1 (en) 2010-06-17 2011-06-01 Reagent microvial with authentication integrated circuit
US13150229 Abandoned US20110312803A1 (en) 2010-06-17 2011-06-01 System for variable loading of reagents into microfluidic device for genetic analysis
US13150059 Abandoned US20110312575A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for nucleic acid amplification using a nicking enzyme and a dna polymerase
US13150135 Expired - Fee Related US8383064B2 (en) 2010-06-17 2011-06-01 Genetic test module with low oligonucleotide probe mass and reagent volumes
US13150100 Abandoned US20110312078A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detecting target nucleic acid sequences in mitochondrial dna
US13150195 Abandoned US20110312790A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with low-volume hybridization chamber
US13149904 Abandoned US20110312630A1 (en) 2010-06-17 2011-06-01 Loc device for pathogen detection, genetic analysis and proteomic analysis with dialysis, chemical lysis, incubation and tandem nucleic acid amplification
US13150095 Abandoned US20110312743A1 (en) 2010-06-17 2011-06-01 Loc device for detection of target nucleic acid sequences using electrodes configured for electrochemiluminescence of luminophores without a coreactant
US13150188 Abandoned US20110312542A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with hybridization array with calibration chamber containing chamber with a blocked inlet spotted with reporter
US13150204 Abandoned US20110312795A1 (en) 2010-06-17 2011-06-01 Diagnostic test module with a loc with integral photosensor and excitation led for detection of hybridization assay results
US13150227 Abandoned US20110309276A1 (en) 2010-06-17 2011-06-01 Fault-tolerant multiple valve assembly with thermal boiling-initiated valve
US13149959 Abandoned US20110312664A1 (en) 2010-06-17 2011-06-01 Microfluidic test module for interfacing with a dedicated reader
US13149983 Abandoned US20110312681A1 (en) 2010-06-17 2011-06-01 Loc device with dialysis section for removing erythrocytes from blood
US13150019 Abandoned US20110312698A1 (en) 2010-06-17 2011-06-01 Microfluidic device with pcr section having short thermal cycle times
US13150164 Abandoned US20110312846A1 (en) 2010-06-17 2011-06-01 Oligonucleotide spotting device with fluidics on both sides of supporting substrate
US13150058 Abandoned US20110312720A1 (en) 2010-06-17 2011-06-01 Loc device for genetic analysis with dialysis and nucleic acid amplification
US13150253 Abandoned US20110312824A1 (en) 2010-06-17 2011-06-01 Test module with waste storage incorporating porous element
US13150053 Expired - Fee Related US8394340B2 (en) 2010-06-17 2011-06-01 Microfluidic test module with low mass electrochemiluminescent probe spots
US13150084 Abandoned US20110312737A1 (en) 2010-06-17 2011-06-01 Single-use test module for electrochemiluminescent detection of targets
US13149910 Abandoned US20110312549A1 (en) 2010-06-17 2011-06-01 Microfluidic device with multi-layer dialysis section
US13149946 Abandoned US20110312652A1 (en) 2010-06-17 2011-06-01 Microfluidic device with low-volume electrochemiluminescence-based probe spots
US13150070 Abandoned US20110312579A1 (en) 2010-06-17 2011-06-01 Loc device with parallel incubation and parallel nucleic acid amplification functionality
US13150129 Abandoned US20110311408A1 (en) 2010-06-17 2011-06-01 Reagent dispensing apparatus
US13150182 Abandoned US20110312604A1 (en) 2010-06-17 2011-06-01 Loc having on-chip electronics for use in a test module to control module communications
US13150037 Abandoned US20110312704A1 (en) 2010-06-17 2011-06-01 Microfluidic device for pcr amplification using low pcr mixture volume
US13150038 Abandoned US20110312540A1 (en) 2010-06-17 2011-06-01 Loc device for detecting target nucleic acid sequences using electrochemiluminescent probes and calibration probes lacking a luminophore
US13150197 Abandoned US20110312792A1 (en) 2010-06-17 2011-06-01 Test module that updates epidemiological databases
US13149908 Abandoned US20110312548A1 (en) 2010-06-17 2011-06-01 Test module with diffusive mixing in small cross sectional area microchannel
US13149935 Abandoned US20110312645A1 (en) 2010-06-17 2011-06-01 Microfluidic device with temperature feedback controlled hybridization chambers for electrochemiluminescent detection of targets
US13149979 Abandoned US20110312555A1 (en) 2010-06-17 2011-06-01 Loc device for detecting hybridization of target nucleic acid sequences with electrochemiluminescent resonant energy transfer, primer-linked, stem-and-loop probes
US13150029 Abandoned US20110312570A1 (en) 2010-06-17 2011-06-01 Microfluidic device for detecting target nucleic acid sequences with probes having long fluorescence lifetime fluorophores
US13150030 Abandoned US20110312701A1 (en) 2010-06-17 2011-06-01 Loc device for electrochemiluminescent detection of target nucleic acid sequences with calibrated photodetection of probes in hybridization array
US13150049 Abandoned US20110312712A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc for pcr amplification of nucleic acids from whole blood
US13150093 Abandoned US20110312741A1 (en) 2010-06-17 2011-06-01 Microfluidic device for analysis of mitochondrial dna
US13150137 Abandoned US20110312081A1 (en) 2010-06-17 2011-06-01 Reagent dispensing apparatus for array of microfluidic devices
US13150196 Abandoned US20110312791A1 (en) 2010-06-17 2011-06-01 Test module with fault-tolerant multiple valve assembly
US13150202 Abandoned US20110312794A1 (en) 2010-06-17 2011-06-01 Test module that updates epidemiological databases with location data
US13149894 Pending US20110312624A1 (en) 2010-06-17 2011-06-01 Microfluidic device with flow-channel structure having active valve for capillary-driven fluidic propulsion without trapped air bubbles
US13149927 Abandoned US20110312075A1 (en) 2010-06-17 2011-06-01 Loc device with parallel incubation and parallel dna and rna amplification functionality
US13149950 Abandoned US20110312655A1 (en) 2010-06-17 2011-06-01 Microfluidic device for pcr, probe hybridization and electrochemiluminescent detection of probe-target hybrids
US13150105 Abandoned US20110312750A1 (en) 2010-06-17 2011-06-01 Microfluidic device with total reagent storage
US13150151 Abandoned US20110312595A1 (en) 2010-06-17 2011-06-01 Microfluidic device with mixing section
US13150231 Abandoned US20110312805A1 (en) 2010-06-17 2011-06-01 Test module with time delayed detection of fluorescence from hybridized probe
US13150243 Abandoned US20110312814A1 (en) 2010-06-17 2011-06-01 Single-use test module with excitation source
US13150087 Abandoned US20110312615A1 (en) 2010-06-17 2011-06-01 Microfluidic device with parallel nucleic acid amplification section
US13150190 Abandoned US20110312788A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc with thermal boiling-initiated valve
US13150094 Abandoned US20110312742A1 (en) 2010-06-17 2011-06-01 Single-use microfluidic device
US13150118 Abandoned US20110312762A1 (en) 2010-06-17 2011-06-01 Loc for detection of hybridization of nucleic acid sequences with fluorescence resonance energy transfer (fret) probes
US13150260 Abandoned US20110312830A1 (en) 2010-06-17 2011-06-01 Genetic analysis loc device with electrochemiluminescent probes having a functional moiety for quenching photon emissions configured to change proximity to a luminophore upon forming a probe-target hybrid
US13150267 Abandoned US20110312836A1 (en) 2010-06-17 2011-06-01 Microfluidic device for electrochemiluminescent detection of target sequences
US13149922 Abandoned US20110312074A1 (en) 2010-06-17 2011-06-01 Microfluidic test module with sample receptacle
US13149971 Abandoned US20110312674A1 (en) 2010-06-17 2011-06-01 Loc device with integral photosensor for electrochemiluminescence based detection of targets
US13150142 Abandoned US20110312591A1 (en) 2010-06-17 2011-06-01 Loc with low-volume hybridization chamber and reagent reservoir for genetic analysis
US13150240 Abandoned