US20060281187A1 - Analyte detection devices and methods with hematocrit/volume correction and feedback control - Google Patents

Analyte detection devices and methods with hematocrit/volume correction and feedback control Download PDF

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US20060281187A1
US20060281187A1 US11/239,122 US23912205A US2006281187A1 US 20060281187 A1 US20060281187 A1 US 20060281187A1 US 23912205 A US23912205 A US 23912205A US 2006281187 A1 US2006281187 A1 US 2006281187A1
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Prior art keywords
sample
arrangement
analyte
assay pad
array
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Jeffrey Emery
Carole Stivers
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Intuity Medical Inc
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Rosedale Medical Inc
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Priority to US11/239,122 priority Critical patent/US20060281187A1/en
Assigned to ROSEDALE MEDICAL, INC. reassignment ROSEDALE MEDICAL, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: EMERY, JEFFREY L., STIVERS, CAROLE R.
Priority to EP06772943.4A priority patent/EP1893994B1/en
Priority to PCT/US2006/022840 priority patent/WO2006138226A2/en
Priority to CA2611891A priority patent/CA2611891C/en
Priority to EP19187252.2A priority patent/EP3629005A1/en
Priority to JP2008516982A priority patent/JP5802361B2/ja
Publication of US20060281187A1 publication Critical patent/US20060281187A1/en
Assigned to INTUITY MEDICAL, INC. reassignment INTUITY MEDICAL, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: ROSEDALE MEDICAL, INC.
Priority to US13/037,089 priority patent/US8969097B2/en
Priority to US14/614,177 priority patent/US9366636B2/en
Priority to US15/177,041 priority patent/US10226208B2/en
Priority to US16/159,546 priority patent/US11419532B2/en
Abandoned legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/15—Devices for taking samples of blood
    • A61B5/157—Devices characterised by integrated means for measuring characteristics of blood
    • A—HUMAN NECESSITIES
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    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
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    • A61B5/14535—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring haematocrit
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    • A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
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    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
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    • G—PHYSICS
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    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
    • G01N21/78—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator producing a change of colour
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    • G01N33/52—Use of compounds or compositions for colorimetric, spectrophotometric or fluorometric investigation, e.g. use of reagent paper and including single- and multilayer analytical elements
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    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
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    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • G01N33/54373—Apparatus specially adapted for solid-phase testing involving physiochemical end-point determination, e.g. wave-guides, FETS, gratings
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    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/66—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood sugars, e.g. galactose
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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0295—Strip shaped analyte sensors for apparatus classified in A61B5/145 or A61B5/157
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N2021/752—Devices comprising reaction zones
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
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    • Y10S435/822—Microorganisms using bacteria or actinomycetales
    • Y10S435/886—Streptomyces
    • Y10S435/895—Streptomyces filipinensis

Definitions

  • the present invention is directed to techniques and devices for detection of the presence and/or concentration of an analyte.
  • diabetes is the fifth-deadliest disease in the United States and kills more than 213,000 people a year, the total economic cost of diabetes in 2002 was estimated at over $132 billion dollars, and the risk of developing type I juvenile diabetes is higher than virtually all other chronic childhood diseases.
  • a critical component in managing diabetes is frequent blood glucose monitoring.
  • a number of systems exist for self-monitoring by the patient.
  • One such system may be termed a photometric system or method.
  • the first step is to obtain the sample of aqueous fluid containing an analyte to be assayed, usually whole blood or fractions thereof.
  • the sample of blood may be obtained by a finger stick or other means.
  • the fluid sample is then contacted with an assay pad or membrane.
  • Contact is generally achieved by moving the assay pad or membrane into contact with the liquid sample on the surface of the patient's skin.
  • the target analyte present in the sample passes through the assay pad or membrane by capillary, wicking, gravity flow and/or diffusion mechanisms. Chemical reagents present in the pad or membrane react with the target analyte producing a light absorbing reaction product, or color change.
  • the assay pad or membrane is then inserted into a monitor where an optical measurement is then made of this color change.
  • the optical measurement is a reflectance measurement
  • a surface of the assay pad or membrane is illuminated with a light source.
  • Light is reflected from the surface of the assay pad or membrane as diffuse reflected light.
  • This diffuse light is collected and measured, for example by the detector of a reflectance spectrophotometer.
  • the amount of reflected light is then related to the amount of analyte in the sample; usually the amount of light reflected off the surface of the assay pad or membrane is an inverse function of the amount of analyte contained in the sample.
  • An algorithm is employed to determine analyte concentration contained in the sample based on the information provided by the detector.
  • Representative algorithms that may be employed where the analyte of interest is glucose and the fluid sample is whole blood are disclosed, for example, in U.S. Pat. Nos. 5,049,487; 5,059,394; 5,843,692 and 5,968,760; the disclosures of which are incorporated herein by reference.
  • Glucose monitoring technology that relies on the photometric method of quantifying the glucose concentration in whole blood may be subject to errors associated with variations in hematocrit level, or concentration of red blood cells within the blood sample.
  • Various methods have been employed to ensure the accuracy and repeatability of measured glucose concentration using the photometric method across a typical range of hematocrit levels.
  • a normal hematocrit level is 42-54% for men and 36-48% for women. Overall, the normal range is from 36-54%, but for a variety of reasons, those who regularly test their glucose concentrations may have hematocrit levels even lower (anemia) or higher (polycythemia) than these normal ranges. This presents a challenge for the development of accurate glucose monitoring.
  • glucose monitors typically require that the user supply a sufficient quantity of whole blood for an accurate reading.
  • This volume has been around 10 microliters or more in the past, but with the development of newer quantification technologies, the minimum volume has been brought to as low as 1 microliter for photometric meters. This has reduced the burden on diabetics in their testing by reducing the depth of the lancing and the effort to milk a relatively large amount of blood from their lancing site. Again, the calibration of the meter is developed with the assumption that this minimum supply has been delivered to the test strip. If the user has not supplied a sufficient amount, then the meter generally displays an error code and the user must test again.
  • a photometric meter may have the ability to evaluate and adjust its internal calibration by detecting the amount of fluid supplied to the reagent strip, and applying an appropriate calibration parameter specifically chosen for that volume.
  • One such device relies on the application of a specific magnitude and duration of a partial vacuum to the skin in order to facilitate the acquisition of a minimum required sample volume.
  • this pre-programmed amount or duration of vacuum may be appropriate.
  • this pre-programmed catalyst may produce either an insufficient or excessive amount of blood, as well as other undesired outcomes, such as excessive bruising (for those with fragile capillary networks), an unnecessary delay in obtaining results (for fast bleeding individuals), as well as excessive residual blood left on the skin.
  • the sample quantification detector could also determine in real-time whether or not a sufficient sample volume has been obtained for an accurate reading, and provide this information as feedback to control the magnitude and/or duration of a catalyst. This feedback driven control would be a significant advantage for integrated glucose monitoring technology.
  • Photometric assay pads or membranes for analyte concentration measurements typically produce a circular or linear spot when the chemical reagents contained therein react with a fluid containing a specific analyte, such as glucose, within whole blood.
  • An ideal spot may be defined as one in which the color across the spot is uniform and indicative of the concentration of the analyte.
  • a spot which is not ideal may be manifest in one or more of the following ways: non-uniformity of the primary color (e.g., variations in the intensity of blue); presence of non-primary color, such as red, which may be associated with the presence and/or lysis of blood cells, and the above color variations may be distributed randomly or non-uniformly across the spot.
  • the quality of a spot developed as a result of an analyte reacting with the reagent membrane may not be ideal as described above.
  • Such reasons may include one or more of: flaws or manufacturing variations in the membrane structure; variations in the concentration of the reagent enzyme; mishandling of the membrane during manufacturing; and unintended chemical reactions between the fluid and/or analyte and the reagent structure and/or membrane chemistry (such as another medical drug within the blood sample reacting with the reagent enzyme).
  • the state of the art has been advanced through the provision of arrangements, devices and techniques such as those described further herein, for accurately, efficiently, and economically determining the presence and/or concentration of an analyte.
  • the state of the art has been advanced, especially, but not exclusively, within the context of personal glucose monitoring devices and techniques. Additionally, or alternatively, according to the present invention arrangements, devices and techniques are provided which may overcome one or more of the abovementioned shortcomings associated with conventional systems and methods.
  • Devices and methods are contemplated that may employ a detector comprising an array of detector elements or pixels to detect color change or intensity of reflected light associated with a photometric chemical reaction between the analyte and reagent chemistry.
  • the detector elements comprise CMOS-based detector elements.
  • the CMOS detector elements help correct for differences in hematocrit levels and/or volumes associated with samples under analysis.
  • An additional aspect of the present invention provides for CMOS-based detector elements that can provide feedback control for a connected device that performs automated whole blood sampling and detection of an analyte.
  • feedback from CMOS detection elements is used to compensate for non-ideal reaction spot characteristics.
  • the present invention provides a device for monitoring the concentration of an analyte present in bodily fluid, the device comprising a detector, the detector comprising a detector element or pixel, the element or pixel comprising a CMOS sensor, a CCD sensor, a photodiode or an infrared sensor, including both near-field and mid-field infrared sensors.
  • Other sensing systems also contemplated within the scope of the present invention include infrared, ultraviolet and fluorescent sensing systems and electrochemical sensing systems, including reagentless sensing approaches.
  • detector array of the present invention may include any suitable detector element(s).
  • the present invention is thus not limited to embodiments of the invention including CMOS or CCD detector elements, photodiodes, infrared, fluorescent, ultraviolet or electrochemical detector elements.
  • the detector array is not limited only to linear arrays.
  • Non-linear arrays such as polar or area arrays, are also contemplated by the present invention.
  • first, second, third and fourth components does not limit the present invention to embodiments where each of these components is physically separable from one another.
  • a single physical element of the invention may perform the features of more than one of the claimed first, second, third or fourth components.
  • a plurality of separate physical elements working together may perform the claimed features of one of the claimed first, second, third or fourth components.
  • reference to first, second (etc.) method steps does not limit the invention to only separate steps.
  • a single method step may satisfy multiple steps described herein.
  • a plurality of method steps could, in combination, constitute a single method step recited herein.
  • an assay pad comprising at least one chemical reagent capable of producing a detectable signal in the form of a reaction spot upon reaction with the analyte
  • a light source comprising at least one chemical reagent capable of producing a detectable signal in the form of a reaction spot upon reaction with the analyte
  • a detector comprising at least one detector
  • a processor capable of producing a detectable signal in the form of a reaction spot upon reaction with the analyte
  • the memory comprising: (a) at least one value indicative of one or more of: (i) the level of hematocrit contained in the sample; (ii) the volume of the sample applied to the assay pad; or (iii) imperfections present in the reaction spot; and (b) at least one algorithm for calculating the concentration of the analyte contained in the sample.
  • devices, arrangements and methods for quantifying the concentration of an analyte present in bodily fluid comprising: providing an assay pad comprising at least one chemical reagent; introducing a sample onto the assay pad; producing a detectable signal in the form of a reaction spot upon reaction of the at least one chemical reagent with the analyte; generating a signal based on light reflected off the assay pad; calculating at least one value indicative to one or more of: (i) the level of hematocrit contained in the sample; (ii) the volume of the sample applied to the assay pad; or (iii) imperfections present in the reaction spot; and calculating the concentration of analyte contained in the sample by factoring in the at least one value.
  • the device may comprise a glucose meter integrating some or all of the above-described features.
  • the integrated device may be configured to perform at least one such photometric analysis before reloading disposable components thereof becomes necessary.
  • the integrated device may be handheld or wearable.
  • the integrated device may be in the general form of a wristwatch.
  • the detector elements may comprise CMOS-based detector elements.
  • the detector array may be in the form of a linear array of CMOS-based detector elements or pixels.
  • an integrated device may include means for extracting a sample of bodily fluid and can comprise a skin piercing member and the application of one or more of: (i) vacuum; (ii) positive pressure; and (iii) heat.
  • the device may further comprise a computer-readable medium, the medium comprising at least one of an algorithm and a look-up table.
  • the device may further comprise a microprocessor controller.
  • the above-described invention may further comprise at least one of a light source, one or more lenses, one or more light transmission elements (e.g. optical fibers), optical diffusers and optical filters.
  • the assay pad may comprise at least one chemical reagent that produces a color change defining a reaction spot upon reaction with the analyte.
  • FIG. 1 is a flow diagram of a mode of operation according to certain aspects of the present invention.
  • FIG. 2 is a schematic illustration of an arrangement formed according to the principles of the present invention.
  • FIG. 3 is a schematic diagram of a portion of the arrangement of FIG. 2 .
  • FIG. 4 is a perspective view of a device formed according to an embodiment of the present invention.
  • FIG. 5 is a partial cutaway view of FIG. 4 .
  • a target analyte such as glucose, bilirubin, alcohol, controlled substances, toxins, hormones, proteins, etc.
  • the current invention provides the ability to correct for broad variations in sample hematocrit levels in the measurement of an analyte, such as glucose, during the course of the test.
  • the invention takes advantage of an imaging array of detectors to perform this correction and does not require any additional hardware. In other words, no other distinct sensors or detectors, other than the imaging array, are required to calculate the correction.
  • the very sensor that is used to quantify the analyte within the sample may also correct for hematocrit.
  • Strategic algorithms that process the data from the imaging array provide real-time or near real-time information about the sample hematocrit level. Thus, more accurate results, regardless of the hematocrit level of the user, may be obtained via correction based on the hematocrit level of the sample.
  • the current invention may also use appropriate algorithms to permit real-time sensing of the amount of sample volume delivered to an assay pad. With this information, appropriate calibration parameters may be selected corresponding to the actual delivered volume. To correct for sample volume, algorithms similar to those used for hematocrit correction may be used, where volume is substituted for hematocrit and a unique formulation and corresponding constants are determined.
  • the present invention offers the flexibility to improve the accuracy of measured glucose for a broad range of sample volumes that are typically delivered to the assay pad of the meter system.
  • sampling catalysts such as vacuum, heat, pressure, etc. may be implemented or provided automatically by the device to help ensure sufficient sample volume is collected and analyzed.
  • the invention provides information to the meter system to know when and how much of the catalyst is sufficient. Since the invention can measure or estimate the volume of the sample delivered to the assay pad, it can also provide feedback to start, maintain or terminate the catalysts, as well as increase or decrease the magnitude of the catalyst, based on this measured volume.
  • the present invention can process data received from the detector array to compensate for irregularities or imperfections present in a reaction spot in order to improve accuracy of the analyte concentration method.
  • the present invention includes devices, arrangements and methods that include any of the above referenced aspects individually, as well as combinations of some or all of these aspects.
  • the current invention may employ a linear CMOS imaging detector array.
  • the linear CMOS array detects light across a single row of optical detectors (pixels) whose output is proportional to the amount of light incident to the pixel.
  • Linear detector arrays offer an advantage over 2-D imaging systems in simplicity and efficiency in processing the image information as long as the expected location of reagent chemistry reaction or reagent spot is known and the associated light, which may be supplied by an LED, is reflected from this area and is imaged appropriately by the CMOS array.
  • the CMOS detector array may have an overall size that is comparable to the size of the assay pad and the expected range of spot sizes that develop on the pad. According to one alternative, the detector can be larger than the size of the pad. This construction can allow wider tolerances in the relative position of the assay pad and the detector, and provide for additional in-process error detection and recovery (e.g., detecting or correcting for assay pad motion).
  • CMOS detector array such as part # TSL1401R or TSL1401CS; from TAOS, Plano, Tex. This detector has 128 pixels across an array of ⁇ 19 mm in length. Light reflected off of white surfaces, such as an unreacted reagent pad, and received by the CMOS detector results in a signal from each pixel that is conditioned to produce a near maximum response up to 5 volts.
  • a number of different arrangements comprising a quantification member, such as an assay pad, a sensor or detector, and one or more additional components are contemplated by the present inventions. Additional exemplary arrangements are described in U.S. application Ser. No. 10/394,230, ANALYTE CONCENTRATION DETECTION DEVICES AND METHODS, the entire content of which is incorporated by reference herein.
  • the senor When coupled with an assay pad containing a photometric reagent, the sensor detects the change in color of the pad, and the output is processed as a change in voltage relative to that of the original reagent color. Typically, about 10-50% of the pixels across the array are sufficient to resolve a spot of color change, but this can depend on a variety of factors, including CMOS sensor design, sample volume size, reagent dynamics, and the optical path between the pad and sensor.
  • a second assay may be performed at a different area of the same assay pad, or on separate assay pad, at a location corresponding to the aforementioned unused pixels.
  • the unused pixels may be used for calibration or as a control.
  • a control solution having a known concentration of analyte may be introduced in the area of the assay pad, or onto a separate pad, in the area of the unused pixels.
  • control solution reacts with the reagent and the signal produced by pixels can be calibrated in accordance with the known analyte concentration.
  • a means for calibrating the reagent for lot information may be provided in the area of the unused pixels, thereby eliminating the need for the user to set reagent lot calibration codes.
  • a similar arrangement and technique would be to utilize a standard color in registry with the unused pixels that produces a known reflectance signal. Upon reading this known signal, the arrangement, via a microprocessor and associated software and electronic components, can verify whether or not the device is functioning properly.
  • sensor data can be acquired with an analog-to-digital capture device, such as a PC board, and processed as a linear dimension data array whose size corresponds to the number of pixels in the imaging array, such as 128 or 256 pixels.
  • This data array will change over time as the reaction between the analyte (glucose) and the reagent enzymes develops, reaches saturation and begins to dry out.
  • the current invention incorporates an algorithm for processing the information in the data array over time to detect and correct for the hematocrit in the blood sample.
  • the rate of color change over time across the detector array, and thus rate of change in signal of the data array, is dependent upon the relative amount of plasma in the sample.
  • a relatively high plasma content in a given sample size will cause the sample to react with the reagent chemistry faster and develop a change in color more quickly than a relatively smaller plasma content. Since hematocrit level is inversely proportional to plasma content, the rate of color change can be scaled inversely to hematocrit level.
  • rate of color change and hematocrit level will depend upon a variety of variables, including the volume of the sample delivered to the assay pad as well as the inherent reagent chemistry, optical path, light source and detector array. Consequently, a unique correlation calibration between color change rate as detected by the CMOS imager and blood hematocrit level can be empirically determined and programmed into a memory device as a lookup table, or calculation.
  • Exemplary, non-limiting algorithm formulations to accomplish the above include:
  • Pixel position x ranges from the lower to upper limits and in the case of a 256 pixel array, would range from 1 to 256.
  • Array signal strength A(x,t) corresponds to a measure of the color of the reagent membrane. Typically, this signal is initially processed as a voltage or a current. Those skilled in the art of photometric reagent signal process will appreciate that subsequent transformation of this data into a measure of normalized reflectance R and/or to absorption via the well-known calculation of K/S may be represented by A(x,t). For example:
  • the appropriate calibration factor relating reflected light to glucose concentration would then be chosen based on the hematocrit level.
  • the meter detects color change and applies the correct calibration factor for the user's hematocrit level to the calculation of glucose content made by an algorithm also contained in the same, or a different memory device.
  • glucose calibration curve is of the form:
  • This corrected signal would then be substituted into the above equation to calculate the hematocrit-adjusted glucose concentration.
  • Processing the data generated by the change in color caused by the reaction between the analyte and reagent chemistry in conjunction with the speed and capacity of today's microprocessors would not add to the required time to process the sample, yet would substantially increase the accuracy and reduce the variability for analyte concentration measurements associated with different whole blood hematocrit levels.
  • Such alternatives and modifications include one or more of: evaluating the rate of pixel signal changes with respect to time; evaluating the rate of pixel change with respect to time and with respect to associated pixels that also are changing (i.e., spatial and temporal rate of change); evaluating the rate of pixel change with respect to time for an individual pixel; evaluating the rate of pixel change with respect to time for multiple pixels; evaluating the rate of pixel change with respect to time for the pixel that detects the largest change in color when enzymatic reaction and color change is complete; evaluating the rate of pixel change with respect to time for the pixel that detects the largest change in color during the ongoing enzymatic reaction; evaluating the rate of pixel change with respect to time for the pixel that detects the largest change in color after a lapse of a predetermined amount of time before any enzymatic reaction has actually occurred; and evaluating the resolved volume of the sample (as described
  • the invention also contemplates novel arrangements, devices and methods for quantifying, in real-time, the amount of sample delivered to an analyte quantification member, such as an assay pad.
  • This method takes advantage of the discrete data provided by individual detector elements or pixels.
  • the system described earlier can resolve a particular dimension associated with the size of the spot, such as width.
  • This invention does not require that the spot be of a particular shape, such as round, square, or rectangular, as long as the detector array is oriented to resolve at least one dimension of the spot that is proportional to sample volume. Assuming the assay pad and the method by which the blood is delivered to the pad has been optimized to reduce the variability in spot development, the spot size will be proportional to the volume of blood sample.
  • the imaging system can resolve the spot size by identifying how many pixels or detector elements have detected a color change. Although the color change associated with the chemical reaction between analyte and enzyme may not be completed or reached equilibrium, the quantification of the number of pixels that have detected a predetermined threshold change in color will be proportional to the spot size. Thus, a real-time assessment of the spot size and thus volume can be computed.
  • the effect on glucose concentration calculations associated with various sample volumes may be empirically determined, and a lookup table, equation, or calculation incorporated in a memory device which may then be used to select an appropriate predetermined calibration factor to provide a more accurate reading of the analyte concentration for a particular sample volume.
  • an appropriate calibration factor based on the actual sample volume may be applied to an algorithm used to calculate glucose concentration.
  • glucose calibration curve is of the form:
  • This corrected signal would then be substituted into the above equation to calculate the volume-adjusted glucose concentration.
  • such alternatives and modifications include one or more of: computing the number of pixels that have detected a change in color above a prescribed constant threshold at a particular point in time during the enzymatic reaction; computing the number of pixels that have detected a change in color above a prescribed constant threshold at multiple points in time during the enzymatic reaction; computing the number of pixels that have detected a change in color above a prescribed constant threshold at a time in which the enzymatic reaction is complete; computing the number of pixels that have detected a change in color above a variable threshold across the array; using above strategies to correlate output to actual sample volume at reagent pad; and using above strategies to predict sample volume to be delivered to assay pad after a predetermined amount of time.
  • the volume information can be used as feedback information, and utilized in devices such as an integrated meter.
  • the definition of an integrated device or meter in this context includes one which includes the functions of acquiring a sample of body fluid or blood from the skin, transporting the body fluid or blood from the skin to a quantification area or assay pad, and quantifying the analyte (e.g.—glucose) in the sample via a photometric method.
  • analyte e.g.—glucose
  • a catalyst such as vacuum, heat, pressure, vibration or similar action is preferably applied to the sampling site to facilitate the acquisition of sufficient sample volume of blood.
  • Catalysts such as these can be effective in expressing sufficiently large volumes of blood even from alternative body sites that are less perfused than the fingertips.
  • this invention provides a construction and method to control the catalyst such that it operates for exactly as long as necessary.
  • the detector array and associated on-board data processing within the integrated device can provide a feedback signal via a digital microprocessor controller or similar device which indicates either to increase, decrease, or keep constant the magnitude of the catalyst, as well as to either continue or stop the application of the catalyst.
  • the control signal may be either binary or analog and use this information accordingly to control a pump (for vacuum/pressure), a motor (for vibration), a heating element (for increasing skin temperature) or combinations thereof.
  • FIG. 1 One such exemplary mode of operation is illustrated in FIG. 1 .
  • a suitable catalyst such as a vacuum created by a suitable mechanism or pump is initiated. Shortly thereafter the signals from the detector array are analyzed and the sample volume estimated. This volume is compared with a target sample volume. If the volume is sufficient, the catalyst is turned off. If the volume is insufficient, the reading and calculating processes are repeated until such time as the target sample volume is reached. Once the target sample volume is reached, the analyte concentration determination may continue.
  • a suitable catalyst such as a vacuum created by a suitable mechanism or pump is initiated. Shortly thereafter the signals from the detector array are analyzed and the sample volume estimated. This volume is compared with a target sample volume. If the volume is sufficient, the catalyst is turned off. If the volume is insufficient, the reading and calculating processes are repeated until such time as the target sample volume is reached. Once the target sample volume is reached, the analyte concentration determination may continue.
  • such alternatives and modifications may include one or more of: providing a feedback signal corresponding to actual sample volume received at the assay pad; providing a feedback signal corresponding to predicted volume anticipated to be delivered to assay pad; providing an analog feedback signal that is proportional to the volume received at the assay pad; providing a digital feedback signal that indicates either sufficient or insufficient quantity of sample volume received; providing feedback signal based on imaging of an alternative location within the meter that is not necessarily the reagent pad, but can also be imaged by the detector array to detect whether a specific threshold of blood will be delivered to the reagent pad; and providing feedback signal based on imaging of an alternative location outside of the meter (such as on the skin) that can also be imaged by the detector array to detect whether a specific threshold of blood will be delivered to the assay pad.
  • the discrete nature of the detection elements or pixels also allows for detection of flaws and to distinguish them from regions of the reaction spot that are developing an appropriate or more ideal photometric reaction, even if they are randomly distributed.
  • a detector array is arranged to scan the reaction spot, optionally coupled with appropriate optical magnification.
  • An ideal spot will produce little or no variation in signal response across the array.
  • the response of the pixels will vary spatially and temporally.
  • a quantification algorithm which has one or more of the following features could correct and/or ignore the reaction spot flaw(s) and have the potential to provide a more accurate measurement of the analyte concentration: identification and inclusion of data only from pixels which correspond to the appropriate and expected color (e.g., screen for data corresponding to various shades of blue only); identification and exclusion of data from pixels which do not correspond to the appropriate and expected color (e.g., screen out data corresponding to shades of red); inclusion/exclusion of pixel information which does not change at a rate with respect to time expected for the appropriate color (e.g., rate of change of blue is not the same as that of non-blue pixels); and inclusion/exclusion of pixel information which does not change at a rate with respect to time after a specific elapsed time or during a specific time window expected for the appropriate color (e.g., blue pixels change from time t 1 to t 2 by x %, whereas non-blue pixels do not change by x % between time t 1 through t 2
  • Combinations of the above strategies or similar ones may allow the algorithm to successfully correct for non-ideal spots. It may even be the case that a relatively small percentage of the spot area actually is ideal, yet if the detector array can image this area, even 1 pixel could be sufficient to provide an accurate reading of the analyte.
  • FIGS. 2-3 are schematic illustrations of at least some of the aspects of arrangements, devices and methods of the present invention.
  • an arrangement 10 such as an integrated device or meter may include a detector array 20 , which can be provided in the form of a linear array of individual detection elements 30 . Each detection element 30 is capable of producing a signal.
  • the detection elements 30 may comprise one or more CMOS-based detection elements or pixels.
  • the linear array 20 is generally in optical registry with an assay pad 40 .
  • the relative vertical position of the assay pad and detector array 20 may, of course, differ from the illustrated embodiment.
  • the assay pad 40 and the detector array 20 may have a geometry that differs from that of the illustrated embodiment.
  • the detector array 20 may be larger than the assay pad 40 .
  • the assay pad 40 preferably contains at least one reagent.
  • a mechanism may be provided to transport a sample of body fluid, such as blood, to the assay pad 40 .
  • a hollow member 60 such as a needle, having one end in fluid communication with the assay pad may provide a mechanism for transport.
  • a reaction between the reagent and the analyte of interest e.g., glucose
  • the detector array 20 corresponds in location to the spot 50 produces a signal in response to the color change that is indicative of the presence of the analyte of interest.
  • the signal can be used to estimate the volume of the sample applied to the reagent pad, monitor the kinetics of the reaction between the reagent and the analyte, and ascertain irregularities in the reaction spot 50 , as described above. This information can then be used to correct the output (e.g., concentration of analyte present in the sample) of the device to account for the hematocrit level, volume of sample presented to the assay pad 40 , and/or irregularities in the reaction spot 50 .
  • the above-described arrangement 10 of features may all be contained or integrated within a single device or meter. Alternatively, one or a combination of any of the above-described features may be incorporated into such a device.
  • the detector array 20 forms part of an arrangement 70 present in the device 10 for carrying out the various operations described herein.
  • the detector 20 may contain a plurality of detector elements in signal communication with a device 72 having timing and control logic.
  • the timing and control logic may include internal as well external control signals. These signals typically include clock and frame start signals. External timing and control signals may be generated by a microprocessor/microcontroller or other external circuitry.
  • the detector array 20 may have analog signal output. Alternatively, the detector 20 may have a digital data interface.
  • the detector may comprise an internal signal amplifier 74 .
  • the signal amplifier 74 may be external, as indicated by the amplifier 74 shown in broken line.
  • the amplifier 74 may be entirely omitted.
  • both an internal and external amplifiers 74 may be provided.
  • the signal from the detector 20 is outputted to an analog/digital converter 76 (where no digital data interface is provided by the detector).
  • the converter 76 is connected to a bus 78 , along with a memory 80 and an input/output device 82 .
  • the memory 80 may comprise one or more of RAM, ROM or EEPROM, as well as other conventional memory devices. Whatever its form, the memory 80 preferably contains at least one value indicative of hematocrit level, sample volume or reagent spot imperfections. In this regard the memory may contain one or more of the algorithms and look-up tables described herein.
  • the converter 76 , the bus 78 , the memory 80 and input/output device 82 may be components of a microprocessor/microcontroller 84 . According to an alternative embodiment, the converter 76 , memory 80 and input/output device 82 are external to the microprocessor/microcontroller 84 .
  • the input/output device 82 is in signal communication with various output devices 86 , 88 , 90 , 92 , and can provide control signals thereto.
  • These output devices may include a device providing a catalyst to facilitate sample acquisition, as described herein.
  • these devices may include one or more of a vacuum pump, an actuation trigger device, a light source, a heat source, a vibration motor, or combinations of any of the foregoing. Regardless of the form of these devices, they are configured and arranged such that they are in signal communication with input/output device 82 so as to be responsive to the control signals.
  • These control signals may be based on sample volume calculations made with the assistance of the detector array, as described herein.
  • An integrated device formed according to the principles of the present invention may have a number of suitable configurations.
  • the device is configured to perform testing by acquiring a sample of blood from the user, transfer the sample to an analysis site, and determine the concentration of a target analyte contained in the sample.
  • These operations are all performed with little or no user input. For example, these operations may commence automatically according to a specified or predetermined schedule. Alternatively, these operations may commence at the command of the user via, for example, pressing a start button on the device.
  • the device may include disposable and reusable portions.
  • the disposable portion may include at least one skin piercing element/transport member and analysis site (which may include an assay pad).
  • the disposable portion may provide the capability to perform a single test. After testing is complete, the disposable portion is discarded and replaced with a new disposable portion before performing another test.
  • the disposable portion includes a plurality of skin piercing elements/transport members and analysis sites. Such disposable units permit a plurality of tests to be performed before it is necessary to discard and replace the disposable unit.
  • the device may be either wearable or handheld, or both.
  • FIGS. 4-5 A non-limiting exemplary integrated device 100 is illustrated in FIGS. 4-5 .
  • the device 100 generally comprises a functional portion 102 , and an optional attachment means or band 104 .
  • the integrated device 100 may be wearable.
  • the integrated device may be operable as a hand-held device.
  • the band 104 can be separated and/or otherwise removed from the user, and the device 100 stored in a suitable case or in the user's pocket. The band can then be grasped and used to hold the device against the skin to perform a testing operation.
  • the device 100 preferably includes at least one arrangement for performing a measurement of the concentration of an analyte contained in a sample of blood.
  • the device 100 comprises at least one skin-piercing element, at least one actuation member, such as a torsional spring element as described in further detail herein, and at least one analysis site 110 , which may contain an assay pad.
  • the at least one arrangement may form part of a disposable portion or unit.
  • the disposable unit allows for at least one measurement of the concentration of an analyte contained in a sample of blood prior to being discarded and replaced.
  • the disposable unit allows for a plurality of measurements of the concentration of an analyte contained in a sample of blood prior to being discarded and replaced.
  • the device may additionally contain one or more of the features disclosed in U.S. Pat. No. 6,540,975, U.S. Patent Application Publications 2003/0153900, 2004/0191119, and published PCT applications WO 04/085995 and WO 04/0191693, the entire contents of which are incorporated herein by reference.

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US11/239,122 US20060281187A1 (en) 2005-06-13 2005-09-30 Analyte detection devices and methods with hematocrit/volume correction and feedback control
JP2008516982A JP5802361B2 (ja) 2005-06-13 2006-06-13 ヘマトクリット／容量の修正及び帰還調節を伴う分析物検出装置及び方法
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EP06772943.4A EP1893994B1 (en) 2005-06-13 2006-06-13 Analyte detection device and method with hematocrit/volume correction
US13/037,089 US8969097B2 (en) 2005-06-13 2011-02-28 Analyte detection devices and methods with hematocrit-volume correction and feedback control
US14/614,177 US9366636B2 (en) 2005-06-13 2015-02-04 Analyte detection devices and methods with hematocrit/volume correction and feedback control
US15/177,041 US10226208B2 (en) 2005-06-13 2016-06-08 Analyte detection devices and methods with hematocrit/volume correction and feedback control
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US20170095188A1 (en) 2017-04-06
US11419532B2 (en) 2022-08-23

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