Classifications

• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
  • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
  • G01N33/483—Physical analysis of biological material
  • G01N33/487—Physical analysis of biological material of liquid biological material
  • G01N33/49—Blood

Definitions

• the present invention relates to medical 15 devices.
• the present invention relates to clinical chemistry analyzers which are used for the measurement of medically significant substances in body fluids.
• optical methods (which are sometimes referred to as spectrophotometric methods) operate on the principle that when specific reagents are mixed with a sample of the body fluid, a reaction takes place which allows the measurement of the chemical of interest by measuring the change in wavelength of light transmitted by the sample.
• the clinical chemistry analyzer systems which use an optical method have typically operated by either mixing the sample with a prepackaged amount of reagents or by allowing the mixing of the sample with the reagents through various tubing and mixing operations.
• the sample In flame photometry, the sample is consumed in a flame.
• the specific light produced by a given chemical of interest during the combustion process is used to determine the level of that chemical in the body fluid.
• Ion selective electrode measurement methods use electrodes having membranes that selectively interact with chemical ions of interest. These methods involve a potentiometric amperometric or other electrical measurement which is a function of the concentration of the ion .of interest in the sample.
• Coated wire electrodes comprising a metal (e.g. platinum) wire coated with a layer of a polymer (e.g. polyvinylchloride) solution mixed with an electroactive species have been developed to solve some of these problems. Coated wire sensors are discussed, for example, in Moody, G.J.
• the spatial relationship of the reference electrode to the sensing electrodes are not fixed one to another.
• these electrodes are constructed in multiple layers over the conductor and each of these layers may have varying characteristics which give varying capacitances and therefore uncontrollable changes in capacitance.
• the capacitance changes continuously with time as the dried hydrophilic layer changes its state of hydration during a test.
• electrodes which have various layers which are not fixed; these can be physically deformed as well, causing additional, uncontrollable changes in capacitance.
• the present invention is an improved clinical chemistry analyzer system which utilizes single-use sensing devices in conjunction with an
• the single-use sensing device receives and holds a sample of the body fluid, and is inserted into a receptacle of the analyzer when a measurement of the concentration of
• the single-use sensing device is removed from the analyzer receptacle and can be discarded.
• the single-use sensing device preferably
• the 20 includes a cavity for holding the sample, a carrier, at least one species sensor, a separate reference sensor, and connection means.
• the species sensor and the reference sensor are supported by the carrier in a fixed spaced relationship so that the species
• connection means engages the receptacle of the analyzer and connects the species sensor and the reference sensor to the
• Each species sensor has a species selective portion which contacts the sample of body fluid and interacts selectively with a selected chemical - 8 - species to cause a characteristic of the species sensor to vary as a function of concentration of that selected chemical species in the sample.
• the reference sensor has a portion which contacts the sample but which does not interact selectively with the selected chemical species so that the corresponding characteristic of the reference sensor does not vary as a function of a concentration of the selected species in the sample.
• the analyzer includes means for deriving a signal from the species sensor and the reference sensor which represents a measured difference in the characteristics of the sensors.
• the analyzer also includes means for determining concentration of the selected chemical species based upon the measured difference. In some embodiments, the analyzer also includes means for calculating other values based upon the concentration.
• the analyzer includes output means for providing an output in human readable form which indicates the concentration of the selected chemical species in the sample or other calculated values of clinical interest.
• This output means preferably includes both a visual display and a device (such as a printer) for providing a permanent printed record of the concentration.
• the output means also includes a communication device for transmitting the output to other equipment (such as a digital computer) for further analysis or storage.
• the single-use sensing device preferably includes machine-readable indicia which identify the particular sensors contained in the sensing device
• the analyzer includes a reader which reads the indicia when the single-use sensing device is inserted in the receptacle.
• the identification information conveyed by the indicia preferably includes the location and identity of each sensor supported by the carrier, calibration data for each species sensor, and a lot or serial number of the sensing device.
• the analyzer uses the information which has been read from the machine-readable indicia by the reader in determining the concentration and in providing an output in human readable form.
• Figure 1 is a perspective view of a preferred embodiment of an analyzer and a disposable sensing device which form the clinical chemistry analyzer system of the present invention.
• Figure 2 is a top view of the disposable sensing device of Figure 1.
• Figure 3 is an electrical block diagram of the analyzer of Figure 1.
• FIGS 4A-4D are perspective views showing other preferred embodiments of the disposable sensing device of the system of the present invention. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
• Analyzer System 10 The preferred embodiment of clinical chemistry analyzer system 10 of the present invention is a compact, self-contained portable system which facilitates usage in a physician's office, an operating room or a clinical chemistry laboratory to measure concentrations of chemicals in blood and other body fluids.
• Analyzer system 10 includes a disposable single-use sensing device 12 which is used in conjunction with analyzer 14.
• Disposable sensing device 12 (which is shown in further detail in Figure 2) includes a plurality of sensors 16A-16E which interact directly with chemicals of interest in the body fluid to provide signals which have a known relationship to concentration of the chemicals of interest in the body fluid. A sample of body fluid is maintained within cavity 18.
• Sensors 16A-16E have their active areas exposed to the interior of cavity 18, so as to interact with the sample of body fluid contained within cavity 18. Cover 19 seals cavity 18 to prevent any spilling or evaporation of the sample and any loss of blood gases from the sample.
• carrier 20 (which is in the form of a flat, generally rigid card) supports sensors 16 and cavity 18.
• Conductors 21A-21E extend between and interconnect sensors 16A-16E and electrical contacts 22A-22E, respectively.
• Electrical contacts 22A-22E are located along a front edge of carrier 20 to make electrical connection with the circuitry of analyzer 14 when disposable sensing device 12 is inserted into receptacle 24 of analyzer 14.
• the particular embodiment of disposable sensing device 12 shown in Figures 1 and 2 is described in further detail in the previously mentioned copending patent application entitled "Disposable Single Use Sensing Device for Clinical Chemistry Analyzer", and that description is hereby incorporated by reference.
• Analyzer 14 includes a housing 26 which contains all of the electronic circuitry used to calculate concentrations of the chemical species of
• analyzer 14 is of a size which is suitable for desk or bench top use, or
• Front panel 28 of analyzer 14 includes keyboard 30 and display 32 which allow an operator to interact and control the operation of analyzer 14.
• Analyzer 14 also preferably includes printer 34 within housing 26. Printer 34 provides a
• This printout is provided on print paper 36 which is fed out of opening 38 in analyzer housing
• analyzer 14 When disposable sensing device 12 is inserted into receptacle 24 of analyzer 14, contacts 20 22A-22E make electrical contact with receptacle connectors 42 of analyzer 14.
• the electrical circuitry of analyzer 14 measures signals from sensors 16A-16E of sensing device 12. Based upon the measured signals, analyzer 14 calculates 25 concentration of the chemicals of interest which have been sensed and, in some cases, other values based upon these concentrations (e.g. sodium-to-potassium ratio and anion gap) .
• concentrations e.g. sodium-to-potassium ratio and anion gap
• sensing device 12 includes four species-selective electrode sensors 16A-16D and a reference electrode 16E which are in the form of thin conductive films deposited on carrier 20, and which are connected by conductors 21A-21E to contacts 22A-22E.
• Sensors 16A-16 ⁇ are located in cavity 18 (which is shown in phantom in Figure 2).
• Each species-selective sensor 16A-16D has a sensor active area within chamber 18 which has a species-selective coating 44A-44D, respectively, which selectively interacts with a particular chemical of interest in the sample of body fluid contained within chamber 18.
• the coating 44A-44D preferably includes a polymer and an electroactive species.
• the polymer serves the functions of creating a membrane over the sensor active area and immobilizing the electroactive species next to the electrically conductive surface of the metallic film of the respective sensors 16A-16D.
• the polymer is, for example, polyvinyl chloride, an epoxy, or a polystyrene which is mixed with an electroactive species in a homogenous fashion to provide a membrane through which the chemical species of interest can diffuse.
• the electroactive species confers the specificity to the sensor.
• the electroactive species of the coating 44A-44D depends, of course, upon the particular chemical species of interest which is to be sensed.
• the electroactive species must interact with the chemical species on a selective basis in a known and predictable manner.
• a salt (calcium di-(octyl- phenyl) phosphonate + dictylphenyl-phosphonate) is one electroactive species which shows good response in the physiological concentration range of 10 to 10 Molar.
• an ionophore (valinomycin) is one effective electroactive species.
• An ionophore is a compound which has the ability to bind a particular ion and transport it across a membrane layer. The binding is detected in the form of a potentiometric charge.
• ion selective electrodes will recognize there are a variety of ionphores and other compounds which will accomplish the same end.
• a spreading layer (not shown) overlies each of the coatings 44A-44D.
• the purpose of the spreading layer is to ensure that the sample contacts the entire surface of coating 44A-44D uniformly.
• reference sensor 16E either has no coating at all, or has a coating 47 which is not specific to the particular chemical species of interest.
• Reference sensor 16E provides a reference from which an electrical measurement can be made by analyzer 14. By measuring an electrical characteristic (e.g. potential, current) between each of the species sensors 16A-16D and reference sensor
• a signal which is a function of chemical concentration of the particular chemical species of interest being sensed by sensors 16A-16D can be obtained. Based upon these signals, the electrical circuitry of analyzer 14 calculates the concentration of the chemical species of interest being measured by sensors 16A-16D. - 14 -
• 16A-16E are of a simple construction which permits use of techniques common to the electronic and anodizing industries to coat conductors with an ion selective layer. Sensors 16A-16E do not require multiple layer construction over the conductor and do not incorporate layers which result in changing capacitance. In fact, in other embodiments of the present invention, the conductors and the species selective coating of sensors 16A-16D are integral rather than having been formed by separate depositions.
• Another important feature of the present invention is that the use of disposable sensing
• OMPI device 12 with analyzer 14 does not require operator calibration (although some calibration capability can be provided as described later, to allow the operator to verify proper operation using a reference solution and make small calibration adjustments). This makes analyzer system 10 of the present invention easier and less time-consuming to use.
• the need for calibration has been particularly critical because the sensing equipment could become contaminated after a number of tests and therefore could produce erroneous results. Even if the sensors did not become contaminated, their characteristics often changed with repeated tests, so that frequent calibration was critical to accurate measurements of chemical concentrations.
• At least one sensing device 12 from each batch or lot of sensing devices 12 is factory-tested by exposing sensors 16 of that device to a solution having known concentrations of each of the species to be sensed. Based upon the signals produced by sensors 16 during this calibration process, a calibration factor is determined for each of the species selective sensors 16A-16D. The calibration data are recorded in the form of machine-readable indicia (such as on coded label 48 as part of a bar code) for all sensing devices 12 of that lot.
• each of the different types of disposable sensing device 12 includes machine-readable, indicia, such as the bar code carried by coded label 48, which includes an identification of the particular sensor associated with each of the electrical contacts 22.
• coded label 48 also contains calibration data and also preferably includes a lot and/or serial number identification of sensing device 12.
• the identification of the particular sensors 16A-16E contained in device 12 can be provided to analyzer 14 by other means.
• different patterns of contacts 22A-22E can designate different groups of sensors 16A-16E.
• each sensing device 12 also preferably includes a "TESTS" identifier printed block or label 52 which lists the particular chemical species which are sensed.
• identifier label 52 is also color coded to simplify selection.
• the species identified by label 52 preferably are factory printed.
• sensing device 12 also contains a "PATIENT NAME” printed block or label 54, a "PATIENT NUMBER” printed block or label 56, and a "LOT NO.” printed block or label 58 (which preferably carries a factory printed lot number and/or serial number).
• the disposable sensing devices 12 of the present invention preferably provide groups of sensors 16 which allow simultaneous testing of concentrations of a group of chemical species which together are useful to a physician or other medical personnel. With the present invention, therefore, tests which are normally performed for patients having particular symptoms or conditions can be
• the groups of species include but are not limited to an "Electrolyte Screening” group, a “Diabetic” group, a “Renal” group, a “Dialysis” group, a “Pregnancy” group, a "Heart” group, an "Emergency” group, a "Neonatal” group, a “Blood Gas” group, an “Operating Room” group, and a “Cancer” group.
• the species sensors used in each of these groups and purposes of each group are described in detail in the previously mentioned patent application "Multiple Species Group Disposable Sensing Device- for Clinical Chemistry Analyzer", and that description is incorporated by reference.
• Analyzer 14 Figure 3 is an electrical block diagram of a preferred embodiment of analyzer 14.
• analyzer 14 includes keyboard 30, display 32, printer 34, connectors 42, code sensor 50, digital microprocessor 60, program memory 62, nonvolatile data memory 64 volatile data memory 66, code reader interface 68, signal conditioning/driver circuit 70, analog multiplexer 72, high stability reference 74, analog-to-digital (A/D) converter 76, temperature sensor 77, battery-powered clock/calendar 78, and communication interface 80.
• Keyboard 30 allows the operator to interact with analyzer 14 by providing input signals to digital microprocessor 60.
• keyboard 30 includes keys which allow the operator to choose particular operations to be performed by analyzer 14, includes keys for entering data such as patient identification numbers and critical concentration limits or ranges which should be flagged by analyzer 14 and includes keys for selecting the units of measurement to be used by analyzer 14.
• Digital microprocessor 60 controls the operation of analyzer 14 and interacts with the other electronic circuitry based upon a stored program contained in program memory 62.
• Microprocessor 60 calculates the concentrations of each of the chemical species of interest and other values based upon those concentrations, and provides outputs through ' display 32, printer 34 and communication interface 80.
• signal conditioning circuit 70 When sensing device 12 is inserted into receptacle 24 of analyzer 14, contacts 22 of sensing device 12 make electrical contact with connectors 42 of analyzer 14, thus connecting sensors 16 to signal conditioning circuit 70.
• the output of signal conditioning circuit 70 is an analog signal for each of the species sensors.
• Analog multiplexer 72 receives the output from signal conditioning circuit 70, together with a high stability reference signal from high stability reference 74. The signals from analog multiplexer 72 are sequentially supplied to
• A/D converter 76 which samples the analog signals and converts them to digital values. These digital values are supplied by A/D converter 76 to digital microprocessor 60.
• temperature sensor 77 also provides a signal to multiplexer 72 which is supplied to A/D converter 76, and converted to a digital value which indicates the temperature.
• This temperature value is used by microprocessor 60 in its concentration calculations and in controlling operation of heater 79 (which is located under cavity 18 when sensing device 12 is inserted in receptacle 24) .
• Heater 79 is operated for those species measurements which require elevated temperatures above room temperature.
• temperature sensor 77 (which is, for example, a thermistor) is mounted in analyzer 14 so that the temperature value produced is representative of ambient temperature and thus approximates the temperature of the sample.
• temperature sensor 77 is mounted on and forms a part of disposable sensing device 12. In those embodiments, temperature sensor 77 may be in contact with the sample.
• A/D converter 76 is basically a ratiometric device - that is, the digital output represents the ratio of the input voltage to an internal reference voltage. As such, the accuracy of the digital output is dependent on the accuracy of the internal reference voltage.
• a second independent stable reference source (high stability reference 74) is periodically measured (for example once each time device 12 is inserted). The value determined by A/D converter 76 for the independent reference voltage from high stability reference 74 is compared with the stored proper value. A variation in the measured value would indicate that either A/D converter 76 and associated elements are producing incorrect results, or that the high stability reference 74 is in error. In either case, the use of high stability reference 74 provides a high degree of
• Code sensor 50 reads coded label 48 carried by sensing device 12.
• Code reader interface 68 receives the output signals from code sensor 50, and converts those signals to digital data which represent the information stored on coded label 48.
• the information carried by coded label 48 preferably includes an identi ication of each of the sensors 16 of sensing device 12, calibration factors for those sensors, and a lot number for sensing device 12.
• code reader 50 is preferably mounted in analyzer 14, in some embodiments it is or includes a hand-held code reader wand which permits the operator to perform the code reading function.
• each of the species selective sensors 16A-16D provides a signal in the form of a potentiometric difference between that sensor 16A-16D and reference sensor 16E which is a function of the concentration of that particular species in the sample of body fluid.
• the relationship between the potentiometric difference and the ion concentration is described by the well-known Nernst equation.
• the particular relationship is not critical, so long as it is a predictable relationship which can be used by digital microprocessor 60 in converting the data from A/D converter 76 to a concentration value.
• microprocessor 60 By knowing the identity of the particular species sensor 16A-16D (based upon data from code reader interface 68) which corresponds to a particular signal from A/D converter 76, microprocessor 60 selects the particular known relationship for that sensor, and converts the sensor data value to a concentration value. This process is repeated for each of the sensor signals. Digital microprocessor 60 also uses the calibration data which was read from coded label 48 and the selected units of measurement (as selected through keyboard 30) in the concentration calculation. As a result, the resulting concentration value represents the concentration based upon the sensor signal, as corrected by the f ctory-determined calibration factor.
• microprocessor 60 uses the calculated concentration values to derive these additional calculated values.
• Microprocessor 60 compares the calculated concentration values (and/or other calculated values) with flag values stored in nonvolatile data memory 64 for the particular species of interest.
• These flag values of concentration ranges or limits are selectable through keyboard 30, and can also include values of ranges which are factory-set and stored in nonvolatile data memory 64.
• the flag values define the normal ranges for each concentration or other calculated value.
• Microprocessor 60 formats the data which are provided through display 32, printer 34, and in preferred embodiments through communication interface 80 (which allows external data transfer to another computer or other external device and which preferably is an RS232 type of interface device).
• the data which are displayed through display 32 and printed in hard copy form by printer 34 preferably includes a patient identification, an identification of the particular chemical species, the concentration value for that species, any other calculated values, the exceeding of any flags and normal and critical ranges which are detected by digital microprocessor 60, the time of day and date (based upon a signal from clock/calendar 78) and the lot and/or serial number of disposable sensing device 12 (which is read from coded label 48 by code sensor 50) .
• the hard copy output from printer 34 allows a permanent record to be maintained of the measurements run by analyzer 14. Inclusion of the lot and/or serial number of each sensing device 12 provides a permanent record which can be used to trace the origin of the sensing device 12 which was used.
• analyzer 14 completes all measurements from the sensors 16, calculates concentrations and - 24 - other values based on concentrations, and displays the calculated values and other information within about one minute or less. Since the species sensors 16A-16D depend upon selective interaction with the species of interest, there is normally a period of time required for equilibrium between the sensor with the sample of body fluid to be reached. In preferred embodiments of the present invention, the polymer/electroactive species coating or mixture of each sensor is selected so that equilibrium has occurred within about ten to about sixty seconds after the sensing device 12 is inserted into receptacle 24 of analyzer 14. This allows the data values from A/D converter 76 to represent end points of the measurement process.
• microprocessor 60 calculates an end point for each sensor based upon one or more data values from A/D converter 76 for that particular sensor. Microprocessor 60 extrapolates the end point based upon data stored in memory 62, 64 or 66, and then calculates, the concentration based upon the extrapolated end point and the calibration data which have been read from coded label 48.
• analyzer 14 Although calibration of analyzer 14 is essentially obviated by the use of encoded calibration data carried by sensing device 12, some embodiments of analyzer 14 include a calibration feature which permits small adjustments to be made to
• keyboard 30 includes a calibration key which, together with the numerical keys of keyboard 30, can be used to enter calibration data for some or all of the sensors.
• the calibration data are derived by the operator by using one of the sensing devices 12 to sense concentrations of species in a reference sample having known concentrations. If the calculated concentration values from analyzer 14 differ from the known values, the operator can provide calibration factors which will bring the values into agreement. These calibration factors are stored and are used by microprocessor 60 in subsequent concentration calculations.
• the clinical chemistry analyzer system 10 of the present invention uses a disposable sensing device 12 having solid state sensors 16 and a microprocessor-based analyzer 14 which does not require intricate mechanical design or intricate tubing or fluidics.
• the system of the present invention is available at a much lower cost than the prior art clinical chemistry analyzers, is light-weight and is portable. This makes the present invention applicable to a wide range of applications which have not been possible previously due to the high cost and lack of portability of the prior art clinical chemistry analyzers.
• the present invention allows comparatively untrained personnel to operate the system. With the present invention, the user is prompted through display 32 in the proper use of analyzer 14.
• the present invention is capable of measuring concentrations of species in whole blood. This eliminates the need for a centrifuge (and the time delays resulting from the centrifuging procedure) . In addition, the volume of the blood sample reuired is less when whole blood is used. With the present invention, maintenance is greatly reduced.
• Analyzer 14 preferably has a minimum of moving parts (primarily associated with printer 34), is simple in mechanical design and does
• Disposable sensing device 12 eliminates the need for calibration, as well as the need for periodic replacement of sensors as required in the prior art. In addition, sensing device 12 reduces the likelihood of any accidental spilling of fluids which could contact and contaminate the electronics of analyzer 14, and eliminates the need for periodic cleaning of analyzer 14.
• Another important advantage of the present invention is the ability of analyzer 14 to function with sensing device 12 having new species sensors without requiring major mechanical revisions to analyzer 14, As sensing devices 12 having new or different sensors are made available, analyzer 14 can be upgraded to accommodate those sensors simply by a change to the program software stored in program memory 62.
• the memory is segmented or sectionalized to simplify and enhance upgradability of analyzer 14 for new sensing devices 12.
• the upgrade modification can be made quickly and simply in the field by service personnel, without requiring that the analyzer 14 be returned to the factory. 4.
• FIGS 1 and 2 show a particularly advantageous form of sensing device 12, it should be recognized that disposable sensing device 12 can take other forms in accordance with the teaching of the present invention.
• Figures 4A-4D show four alternative embodiments of the disposable sensing device of the present invention.
• disposable sensing device 12A includes a circular base 100 which supports and holds four metallic wire electrodes 102A-102D in fixed spaced relationship to one another.
• a cylindrical tube 104 is bonded to base 100 to form a cavity 106 for receiving and holding a fluid sample.
• each of the wire electrodes 102A-102D extends upwardly into cavity 106.
• a coating 108A-108D is provided on the upper ends of wires 102A-102D, respectively.
• coatings 108A, 108B and 108C are different species selective coatings which are generally similar to the coatings 44A-44C described with reference to disposable sensing device 12 of Figure 2.
• Coating 108D is a reference coating which is not species selective with respect to any of the species with which coatings 108A-108C selectively interact.
• wires 102A-102D extend below base 100 to form the electrical contacts which are connected to the electrical circuitry of analyzer 14 when disposable sensing device 12A is inserted into a receptacle in analyzer 14. Due to the differences between the shape of sensing device 12 shown in Figures 1 and 2 and sensing device 12A shown in Figure 4A, the shape of the corresponding receptacle in analyzer 14 which receives and mates with sensing device 12A must be different than in the embodiment shown in Figure 1. In the case of sensing device 12A, the receptacle in analyzer 14 is in the form of a socket with female connectors for receiving wires 102A-102D rather than a slot like receptacle 24 shown in Figure 1.
• OMPI Sensing device 12A also includes a coded label 48A on the outer surface of cylinder 104.
• Label 48A contains machine-readable indicia, such as in the form of a bar code, which provide information identifying the particular species to be sensed by each of the wire electrodes 102A-102D, calibration factors for those electrodes, and lot/serial number identification of device 12A.
• Coded label 48A is read by analyzer 14 when disposable sensing device 12A is inserted into the cooperating receptacle.
• FIG 4B shows another embodiment of the present invention which uses coated wire electrodes as the sensor elements.
• disposable sensing device 12B is a two-part assembly which includes tube 120 and carrier 122.
• Tube 120 defines a cavity 124 for holding a sample of body fluid.
• Carrier 122 which is inserted into cavity 124, supports four wire electrodes 126A-126D in fixed spaced relationship to one another.
• the upper ends of electrodes 126A-126D extend out the top of carrier 122 and above the top edge of tube 120 to provide electrical connection between analyzer 14 and sensing device 12B.
• the lower ends of wire electrodes 126A-126D extend out the bottom of carrier 122 so as to contact the sample of body fluid contained in chamber 124.
• Electrodes 126A, 126B and 126C are coated with species selective coatings 128A-128C, respectively.
• Reference electrode 126D also preferably includes a coating 128D on its lower end. Unlike the coatings 128A-128C, reference coating 128D is not species selective.
• Coded label 48B is attached to the outer surface of tube 120, and contains a machine-readable code which identifies each of the wire electrodes 126A-126D and provides calibration factors and lot/serial identification numbers.
• sensing device 12B shown 5 in Figure 4B requires still a different type of receptacle from the type required by either disposable sensing device 12A or disposable sensing device 12.
• wire electrodes 124A-124D have their upper ends extending
• the mating receptacle of analyzer 14 therefore, is of a form which has its connecting socket positioned above rather than below sensing device 12B.
• Figure 4C shows an embodiment of the present
• sensing device 12C includes a circular base 130 which supports four pin electrodes 132A-132D in fixed spaced relationship to
• pins 132A-132D extend out the bottom of base 130 to connect to the electrical connectors of the receptacle of analyzer 14.
• Cylinder 134 is bonded to base 130 to
• pin electrodes 132A-132D are exposed to the sample of body fluid.
• the pin heads of pin electrodes 132A, 132B and 132C have species selective
• coded label 48C is attached to the outer surface of cylinder 134.
• the machine-readable code contained in coded label 48C identifies pin electrodes 132A-132D, provides calibration data for each electrode, and provides lot and/or serial number identification of sensing device 12C.
• FIG 4D shows still another embodiment of the present invention which uses flat film sensing electrodes and a two-part sensing device assembly.
• Sensing device 12D includes tube 150 and carrier 152.
• Tube 150 defines a cavity 154 for receiving and holding a sample of the body fluid to be analyzed.
• Carrier 152 is inserted into cavity 154, and supports flat film electrodes 156A-156D.
• flat film electrodes 156A and 156B are vertical electrodes positioned on the back side of carrier 152, while electrodes 156C and 156D are located on the front side of carrier 152.
• Each sensor electrode 156A-156D is exposed at the upper end of carrier 152 to permit connection to a mating receptacle of analyzer 14.
• electrodes 156A-156D include coatings which (in the case of electrodes 156A-156C) selectively interact with predetermined species which are contained in the sample of body fluid.
• coating 158C at the lower end of electrode 156C and reference coating 158D at the lower end of reference electrode 156D are shown.
• disposable sensing device 12D also includes a coded label 48D which is attached to the outer surface of tube 150.
• coded label 160 identifies each of the sensor electrodes 156A-156D, provides calibration
• the clinical analyzer system of the present ⁇ invention provides physicians and other medical personnel with the ability to conduct basic chemistry tests on whole blood and other body fluids without delay and at reasonable cost.
• the simplicity of the analyzer and disposable sensing device, and the ease of use and lack of maintenance makes the system of the present invention both affordable and convenient for doctors' offices, physician group practices, bedside applications in hospitals, operating and emergency rooms, cardiac and intensive care units, nursing homes, ambulances and emergency vehicles, "stat" use in hospital clinical laboratories, and other applications” (such as veternarians' offices and clinics) where clinical chemistry instrumentation has either not been available or has not been cost and time effective.

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• 1984
  • 1984-11-08 JP JP50429884A patent/JPS61500508A/ja active Pending
  • 1984-11-08 WO PCT/US1984/001814 patent/WO1985002257A1/en not_active Application Discontinuation
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