CA1291795C - Blood analyzer - Google Patents
Blood analyzerInfo
- Publication number
- CA1291795C CA1291795C CA000514031A CA514031A CA1291795C CA 1291795 C CA1291795 C CA 1291795C CA 000514031 A CA000514031 A CA 000514031A CA 514031 A CA514031 A CA 514031A CA 1291795 C CA1291795 C CA 1291795C
- Authority
- CA
- Canada
- Prior art keywords
- sample
- standardizing
- conductivity
- flow path
- concentration
- 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.)
- Expired - Lifetime
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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
- G01N33/4915—Blood using flow cells
Abstract
Abstract of the Disclosure A blood analyzer that measures hematocrit levels as well as electrolyte and blood gas concentrations. Specific features of the analyzer include a removable septum assembly, an electrode assembly, and means for measuring conductivity to determine hematocrit using standardizing solutions.
Description
~29i795 BLOOD ANALYZER
Background of the Invention This invention relates to blood analyzers used to measure various components in a blood sample, for example in medical diagnosis and research.
The ratio of the volume of packed red blood cells from a whole blood sample to the total sample volume is a useful measurement for diagnosing anemia and other disease conditions. That ratio usually is referred to as the "hematocrit ratio" or the "hematocrit value", and it is usually determined by centrifuging a whole blood sample to separate cells from plasma. It is known that, all other things being constant, the conductivity of a blood sample varies as a function of its hematocrit value, but other blood components, notably electrolytes, influence conductivity significantly, and the conductivity of those components must be accurately accounted ~or if a reliable hematocrit value is to be derived from conductivity readings.
Automated equipment for determining blood components, such as electrolyte concentration or dissolved blood gas partial pressures, often involve the use of electrodes positioned along a flow path. When whole blood is introduced in the flow path, the electrodes provide a reading of the desired blood characteristic. Currently, electrodes are available to provide electrical signals representative of various blood components such as sodium ion concentration ("[Na ]"), potassium ion concentration ("lK ]"), calcium ion concentration ("~Ca ]"), hydrogen ion concentration (npH"), partial pressure attributed to ~k ~91~9S
Background of the Invention This invention relates to blood analyzers used to measure various components in a blood sample, for example in medical diagnosis and research.
The ratio of the volume of packed red blood cells from a whole blood sample to the total sample volume is a useful measurement for diagnosing anemia and other disease conditions. That ratio usually is referred to as the "hematocrit ratio" or the "hematocrit value", and it is usually determined by centrifuging a whole blood sample to separate cells from plasma. It is known that, all other things being constant, the conductivity of a blood sample varies as a function of its hematocrit value, but other blood components, notably electrolytes, influence conductivity significantly, and the conductivity of those components must be accurately accounted ~or if a reliable hematocrit value is to be derived from conductivity readings.
Automated equipment for determining blood components, such as electrolyte concentration or dissolved blood gas partial pressures, often involve the use of electrodes positioned along a flow path. When whole blood is introduced in the flow path, the electrodes provide a reading of the desired blood characteristic. Currently, electrodes are available to provide electrical signals representative of various blood components such as sodium ion concentration ("[Na ]"), potassium ion concentration ("lK ]"), calcium ion concentration ("~Ca ]"), hydrogen ion concentration (npH"), partial pressure attributed to ~k ~91~9S
2 ("PO2")~ and partial pressure attributed to CO2 ("PCO2"). From time to time it may be necessary to replace various components of a blood analyzer flow path, such as an electrode or a rubber inlet septum.
Moreover, particularly in analyzers with a small, tortuous flow path having dead spots, whole blood may clot, resulting in lost time from shut-down, disassembly, cleaning, re-assembly, and re-starting of the apparatus.
SummarY _ the Invention In one aspect of the invention, the hematocrit level of a blood sample is measured by flowing the sample along a liquid flow path and using means in the flow path to obtain electrical signals representative of the sample's electrical conductivity and of the concentration of an ion species in the sample.
Standardizing solution is introduced in the same flow path, either before or after the sample measurement.
The standardizing solution has a known ion species concentration and a conductivity indicative of a known equivalent hematocrit value; "equivalent" hematocrit value is used in this application to mean the hematocrit level of a blood sample having a conductivity corresponding to that of the standardizing solution, even though the standardizing solution contains no whole blood cells and has an actual hematocrit value of 0.
Electrical signals are obtained for standardizing solution conductivity and ion species concentration. A
tentative sample hematocrit value is derived from the sample and standardizing conductivity signals, with reference to the known equivalent standardizing hematocrit value. Then the tentative hematocrit value is corrected with reference to the sample and standardizing ion concentration signals and to the known standardizing solution ion concentration value.
In preferred embodiments of the method, an external validation of the apparatus is provided from time to time by introducing a control solution into the flow path, which is described below in connection with the third aspect of the invention. Also in preferred embodiments, conductivity of solutions in the flow path is obtained by: a) providing electrodes in the flow path coupled to a constant current AC circuit via a transformer; b) applying an AC signal from the AC
circuit to the electrodes via the transformer; and c) detecting reflected impedance in the AC circuit. The method comprises: a) obtaining the electrical signals 1~ representative of standardizing conductivity and standardizing ion concentration; b) storing signals representative of the known standardizing equivalent hematocrit value and the known standardizing ion concentration value; c) obtaining the electrical signals representative of sample concentration and standardizing ion concentration; d) comparing the sample and the standardizing ion concentration signals with reference to the stored known standardizing value signal, to derive a signal representative of sample ion concentration value; e) comparing the sample and the standardizing conductivity signals with reference to the stored standardizing hematocrit value signal to derive a signal representative of a tentative sample hematocrit value; and f) correcting the tentative sample hematocrit value signal with reference to the sample ion concentration signal and the stored standardizing ion concentration value signal. Preferred ion species for use in the method are Na+ or Cl .
The invention also features, in another aspect, apparatus for determining hematocrit value in a blood sample comprising: 1) means for providing a fluid flow path; 2) means in the flow path for providing an electrical signal representative of the conductivity of liquid passing along the flow path; 3) means in the flow path for providing a signal representative of the concentration of an ion species in liquid passing along the flow path; 4) means for introducing the blood sample into the flow path to obtain a signal representative of sample conductivity and of sample ion species concentration; 5) means for introducing into the flow path a standardizing solution having a known concentration of an ion species and having a conductivity representative of a known equivalent hematocrit value; 6) means for deriving a signal representative of a tentative sample hematocrit value from the sample conductivity signal, with reference to the standardizing conductivity signal, and to the standardizing equivalent hematocrit value; and 7) means for correcting the tentative sample hematocrit value with reference to the standardizing and sample ion concentration signals and to the known standardizing ion concentration.
In preferred embodiments the apparatus includes: a) means for storing either the sample or the standardizing conductivity signal, and means for comparing the conductivity signals with reference to the known standardizing equivalent hematocrit value to generate a signal representative of the tentative sample hematocrit value; and b) means for correcting the tentative sample hematocrit value signal including means for storing either the standardizing or the sample ion 9~79~i concentration signal and comparing the ion concentration signals with reference to the known standardizing ion concentration value. The apparatus comprises at least two standardizing solutions, each of which has a conductivity indicative of a known equivalent hematocrit value and a known ion concentration. The conductivity measuring means comprises electrodes in the flow path, a constant current AC circuit coupled to the electrodes via a transformer and means for detecting the reflected impedance in the AC circuit. Specifically, the conductivity signal-generating means comprises: 1) a first transformer for coupling the AC circuit to the electrodes; and 2) a second transformer for maintaining constant current in the AC circuit; means establishing a loop between the electrodes and means, connected in the loop between the second transformer and the electrodes, selected to compensate for inherent capacitance at the electrode/sample interface. The apparatus comprises an ion species sensing electrode positioned in the flow path and connected via an electrical output circuit connected to the input of a multiplexer, the impedance detecting means also being connected to the input of the multiplexer, the multiplexer having an output means connected via an analog-to-digital converter to a means for storing and comparing signals, and to the means for correcting sample conductivity.
In a third aspect the invention features a control solution kit for evaluating the hematocrit detection apparatus. The solution comprises an aqueous solution of the ion species (e,g. Na or Cl ) at a known concentration; and an ion activity enhancing agent (e.g. a polyol selected from glycerol and polyalkyl 179~5 glycols). The solution has a conductivity representative of a known equivalent hematocrit level, and both the ion concentration and the equivalent hematocrit value preferably are within physiological ranges (e.g., [Na ] is between 130-150 mM, and hematocrit is between 40 and 55%).
The hematocrit measurement aspects of the invention provide rapid, accurate highly automated measurements of the hematocrit level, without the need for the analyzer user to store whole blood standards .
Other features and advantages of the invention will be apparent from the following description of the preferred embodiment and from the claims.
Description _ the Preferred Embodiment We first briefly describe the drawings.
I. Drawinqs Fig, 1 is a front view of a blood analyzer.
Fig. 2 i8 a diagrammatic representation of the fluid flow path and some of the electrical components of the analyzer of Fig. 1.
Fig. 3 is a side view, in section, of the septum assembly and septum mounting plate of the analyzer of Fig. 1.
Fig. 4 is a view along 4-4 of Fig. 5.
Fig. 4A is a section of a septum from the septum assembly of Fig. 3.
Fig. 5 is an exploded view, with parts broken away, of the septum assembly and mounting plate of Fig.
Moreover, particularly in analyzers with a small, tortuous flow path having dead spots, whole blood may clot, resulting in lost time from shut-down, disassembly, cleaning, re-assembly, and re-starting of the apparatus.
SummarY _ the Invention In one aspect of the invention, the hematocrit level of a blood sample is measured by flowing the sample along a liquid flow path and using means in the flow path to obtain electrical signals representative of the sample's electrical conductivity and of the concentration of an ion species in the sample.
Standardizing solution is introduced in the same flow path, either before or after the sample measurement.
The standardizing solution has a known ion species concentration and a conductivity indicative of a known equivalent hematocrit value; "equivalent" hematocrit value is used in this application to mean the hematocrit level of a blood sample having a conductivity corresponding to that of the standardizing solution, even though the standardizing solution contains no whole blood cells and has an actual hematocrit value of 0.
Electrical signals are obtained for standardizing solution conductivity and ion species concentration. A
tentative sample hematocrit value is derived from the sample and standardizing conductivity signals, with reference to the known equivalent standardizing hematocrit value. Then the tentative hematocrit value is corrected with reference to the sample and standardizing ion concentration signals and to the known standardizing solution ion concentration value.
In preferred embodiments of the method, an external validation of the apparatus is provided from time to time by introducing a control solution into the flow path, which is described below in connection with the third aspect of the invention. Also in preferred embodiments, conductivity of solutions in the flow path is obtained by: a) providing electrodes in the flow path coupled to a constant current AC circuit via a transformer; b) applying an AC signal from the AC
circuit to the electrodes via the transformer; and c) detecting reflected impedance in the AC circuit. The method comprises: a) obtaining the electrical signals 1~ representative of standardizing conductivity and standardizing ion concentration; b) storing signals representative of the known standardizing equivalent hematocrit value and the known standardizing ion concentration value; c) obtaining the electrical signals representative of sample concentration and standardizing ion concentration; d) comparing the sample and the standardizing ion concentration signals with reference to the stored known standardizing value signal, to derive a signal representative of sample ion concentration value; e) comparing the sample and the standardizing conductivity signals with reference to the stored standardizing hematocrit value signal to derive a signal representative of a tentative sample hematocrit value; and f) correcting the tentative sample hematocrit value signal with reference to the sample ion concentration signal and the stored standardizing ion concentration value signal. Preferred ion species for use in the method are Na+ or Cl .
The invention also features, in another aspect, apparatus for determining hematocrit value in a blood sample comprising: 1) means for providing a fluid flow path; 2) means in the flow path for providing an electrical signal representative of the conductivity of liquid passing along the flow path; 3) means in the flow path for providing a signal representative of the concentration of an ion species in liquid passing along the flow path; 4) means for introducing the blood sample into the flow path to obtain a signal representative of sample conductivity and of sample ion species concentration; 5) means for introducing into the flow path a standardizing solution having a known concentration of an ion species and having a conductivity representative of a known equivalent hematocrit value; 6) means for deriving a signal representative of a tentative sample hematocrit value from the sample conductivity signal, with reference to the standardizing conductivity signal, and to the standardizing equivalent hematocrit value; and 7) means for correcting the tentative sample hematocrit value with reference to the standardizing and sample ion concentration signals and to the known standardizing ion concentration.
In preferred embodiments the apparatus includes: a) means for storing either the sample or the standardizing conductivity signal, and means for comparing the conductivity signals with reference to the known standardizing equivalent hematocrit value to generate a signal representative of the tentative sample hematocrit value; and b) means for correcting the tentative sample hematocrit value signal including means for storing either the standardizing or the sample ion 9~79~i concentration signal and comparing the ion concentration signals with reference to the known standardizing ion concentration value. The apparatus comprises at least two standardizing solutions, each of which has a conductivity indicative of a known equivalent hematocrit value and a known ion concentration. The conductivity measuring means comprises electrodes in the flow path, a constant current AC circuit coupled to the electrodes via a transformer and means for detecting the reflected impedance in the AC circuit. Specifically, the conductivity signal-generating means comprises: 1) a first transformer for coupling the AC circuit to the electrodes; and 2) a second transformer for maintaining constant current in the AC circuit; means establishing a loop between the electrodes and means, connected in the loop between the second transformer and the electrodes, selected to compensate for inherent capacitance at the electrode/sample interface. The apparatus comprises an ion species sensing electrode positioned in the flow path and connected via an electrical output circuit connected to the input of a multiplexer, the impedance detecting means also being connected to the input of the multiplexer, the multiplexer having an output means connected via an analog-to-digital converter to a means for storing and comparing signals, and to the means for correcting sample conductivity.
In a third aspect the invention features a control solution kit for evaluating the hematocrit detection apparatus. The solution comprises an aqueous solution of the ion species (e,g. Na or Cl ) at a known concentration; and an ion activity enhancing agent (e.g. a polyol selected from glycerol and polyalkyl 179~5 glycols). The solution has a conductivity representative of a known equivalent hematocrit level, and both the ion concentration and the equivalent hematocrit value preferably are within physiological ranges (e.g., [Na ] is between 130-150 mM, and hematocrit is between 40 and 55%).
The hematocrit measurement aspects of the invention provide rapid, accurate highly automated measurements of the hematocrit level, without the need for the analyzer user to store whole blood standards .
Other features and advantages of the invention will be apparent from the following description of the preferred embodiment and from the claims.
Description _ the Preferred Embodiment We first briefly describe the drawings.
I. Drawinqs Fig, 1 is a front view of a blood analyzer.
Fig. 2 i8 a diagrammatic representation of the fluid flow path and some of the electrical components of the analyzer of Fig. 1.
Fig. 3 is a side view, in section, of the septum assembly and septum mounting plate of the analyzer of Fig. 1.
Fig. 4 is a view along 4-4 of Fig. 5.
Fig. 4A is a section of a septum from the septum assembly of Fig. 3.
Fig. 5 is an exploded view, with parts broken away, of the septum assembly and mounting plate of Fig.
3.
Fig. 6 is a side view of the electrode holder assembly of the analyzer of Fig. 1.
Fig. 7 is a view, in section, along 7-7 of Fig.
6.
17~5 Fig. 8 is a side view of the holder assembly of Fig. 6 with parts exploded, broken away, and in section.
Fig. 8A is a view of the reference block of the assembly of Fig. 6, taken along 8A-8A of Fig. 8.
5Fig. 9 is a view along 9-9 of Fig. 8 with parts broken away and in section.
Fig. 10 is a view, in section, along 10-10 of Fig. 8.
Fig. 11 is a plan side view of an electrode clip for use in the assembly of Fig. 6.
Fig.-12 is a diagrammatic representation of electronic components and functions related to the hematocrit detector of the analyzer of Fig. 1.
Fig. 12A is a graph of the reciprocal of resistivity versus l/(l-hematocrit value).
Fig. 13 is a diagrammatic representation of the electrical functions of the analyzer of Fig. 1.
II. Structure Analyzer 10 of Fig. 1 provides for measurement of the concentrations of certain electrolytes and gases in a small (e.g. less than aboùt 0.25 ml) sample of whole blood that has been treated (e.g. with heparin) to prevent coagulation. Specifically, the treated sample is drawn from its container through a probe 20, along a sample flow path, and out a waste outlet 28 (Fig. 2).
Readings of sample PO2, PCO2, [Na ], lK ~, [Ca ], and pH are provided on a C.R.T. display 12 and a tape printer 14. The same flow path includes means to provide a measurement and readout of the sample hematocrit value.
The above measurements are performed as described in greater detail below, using electrodes and associated components that yield an electric signal ~ ?~9~ 5 - representative of the characteristic being measured. In order to ascribe a value to the signal, the electrodes are standardized periodically with standard gases from replaceable cylinders and with standard fluids frorn a replaceable fluid pack 18 whose components and operation are also described below. The operation of the electrodes and standardizing apparatus is controlled by a computer 130 (Fig. 13) in response to a control program and to the operator's entries on keypad 16.
A. SamPle Flow Path As il,lustrated in Fig. 2, probe 20 is a hollow elongated metal tube (e.g. stainless steel~ having a fluid inlet 21 at one end and connected at the other end to a fluid flow path. A probe drive motor 22, controlled by controller 222, movPs the probe longitudinally through septum assembly 24, while the probe outlet remains in communication with the fluid flow path. The furthest longitudinal extension of the probe in the direction of arrow A is shown in Fig. 2, with probe inlet 21 positioned outside the septum assembly, immersed in a sample 26 that is to be drawn through the inlet and along the flow path.
Fig. 2 diagrams the sample flow path through an electrode assembly (best shown in Figs. 6-10 and described in greater detail below) that includes: a heater block 30 heated by a resistance heater 160; a series of six electrodes, 31, 33, 35, 37, 39, and 41 in an electrode block 80 that enable generation of signals representative of PO2, PCO2, pH, [Ca ], LK ], and [Na ], respectively; and a reference block 105.
The external, mechanical configuration of the electrodes is described below; the electrochemical principles and composition of the electrodes are conventional. From .
, . .
P?~9~7~5 g electrode block 80, the sample flows to waste outlet 28. The fluid flow is drawn along the path by a peristaltic pump 29, driven by stepper motor 230 under the control of controller 229.
Along the flow path, there are air detectors to sense conductivity changes representative of the change from air to liquid, thereby providing an indication of air/liquid transitions and thus to signal changes from one fluid to another and to verify sample and standard positioning. Specifically, one air detector 32 is positioned in heating block 30, and a detector 69 located in heater block 30 serves as a hematocrit level detector as described in greater detail below. A third air detector 103 is located in the electrode block.
Finally, a clamp electrode 43 is positioned upstream from waste outlet 28 to connect to circuitry that minimizes the common mode voltage range and thereby improves the sensitivity and stability of the electrode measurement.
B. Standard Flow Paths The analyzer has been designed particularly to flow the various standard fluids through the flow path and to flush the flow path, while minimizing any opportunity for contamination between standards, or between a standard and a blood sample. As best shown in Fig. 2, the standards are assigned to specific flow paths and chambers in septum assembly 24, and from there, the standards flow through the above-described sample flow path to waste outlet 28. The various standards and their flow paths are:
7~5 1) GA, which is a source of gas having known PO2 and PCO2 composition, connected via metering solenoid valves 46 (sold by Lee Company, Westbrook, Conn.) to a humidifier 47 and thence, via line 48 to chamber 49 of the septum assembly 24.
2) GB, which is similar to GA, having different PO2 and PCO2 composition, thereby enabling standardization of those two electrodes; GB col~municates with chamber 49 of septum assembly 24 via solenoid valves 46', humidifer 47' and line 48'.
3) pHA, a liquid of known pH that flows via line 53 to chamber 54 of septum assembly 24;
Fig. 6 is a side view of the electrode holder assembly of the analyzer of Fig. 1.
Fig. 7 is a view, in section, along 7-7 of Fig.
6.
17~5 Fig. 8 is a side view of the holder assembly of Fig. 6 with parts exploded, broken away, and in section.
Fig. 8A is a view of the reference block of the assembly of Fig. 6, taken along 8A-8A of Fig. 8.
5Fig. 9 is a view along 9-9 of Fig. 8 with parts broken away and in section.
Fig. 10 is a view, in section, along 10-10 of Fig. 8.
Fig. 11 is a plan side view of an electrode clip for use in the assembly of Fig. 6.
Fig.-12 is a diagrammatic representation of electronic components and functions related to the hematocrit detector of the analyzer of Fig. 1.
Fig. 12A is a graph of the reciprocal of resistivity versus l/(l-hematocrit value).
Fig. 13 is a diagrammatic representation of the electrical functions of the analyzer of Fig. 1.
II. Structure Analyzer 10 of Fig. 1 provides for measurement of the concentrations of certain electrolytes and gases in a small (e.g. less than aboùt 0.25 ml) sample of whole blood that has been treated (e.g. with heparin) to prevent coagulation. Specifically, the treated sample is drawn from its container through a probe 20, along a sample flow path, and out a waste outlet 28 (Fig. 2).
Readings of sample PO2, PCO2, [Na ], lK ~, [Ca ], and pH are provided on a C.R.T. display 12 and a tape printer 14. The same flow path includes means to provide a measurement and readout of the sample hematocrit value.
The above measurements are performed as described in greater detail below, using electrodes and associated components that yield an electric signal ~ ?~9~ 5 - representative of the characteristic being measured. In order to ascribe a value to the signal, the electrodes are standardized periodically with standard gases from replaceable cylinders and with standard fluids frorn a replaceable fluid pack 18 whose components and operation are also described below. The operation of the electrodes and standardizing apparatus is controlled by a computer 130 (Fig. 13) in response to a control program and to the operator's entries on keypad 16.
A. SamPle Flow Path As il,lustrated in Fig. 2, probe 20 is a hollow elongated metal tube (e.g. stainless steel~ having a fluid inlet 21 at one end and connected at the other end to a fluid flow path. A probe drive motor 22, controlled by controller 222, movPs the probe longitudinally through septum assembly 24, while the probe outlet remains in communication with the fluid flow path. The furthest longitudinal extension of the probe in the direction of arrow A is shown in Fig. 2, with probe inlet 21 positioned outside the septum assembly, immersed in a sample 26 that is to be drawn through the inlet and along the flow path.
Fig. 2 diagrams the sample flow path through an electrode assembly (best shown in Figs. 6-10 and described in greater detail below) that includes: a heater block 30 heated by a resistance heater 160; a series of six electrodes, 31, 33, 35, 37, 39, and 41 in an electrode block 80 that enable generation of signals representative of PO2, PCO2, pH, [Ca ], LK ], and [Na ], respectively; and a reference block 105.
The external, mechanical configuration of the electrodes is described below; the electrochemical principles and composition of the electrodes are conventional. From .
, . .
P?~9~7~5 g electrode block 80, the sample flows to waste outlet 28. The fluid flow is drawn along the path by a peristaltic pump 29, driven by stepper motor 230 under the control of controller 229.
Along the flow path, there are air detectors to sense conductivity changes representative of the change from air to liquid, thereby providing an indication of air/liquid transitions and thus to signal changes from one fluid to another and to verify sample and standard positioning. Specifically, one air detector 32 is positioned in heating block 30, and a detector 69 located in heater block 30 serves as a hematocrit level detector as described in greater detail below. A third air detector 103 is located in the electrode block.
Finally, a clamp electrode 43 is positioned upstream from waste outlet 28 to connect to circuitry that minimizes the common mode voltage range and thereby improves the sensitivity and stability of the electrode measurement.
B. Standard Flow Paths The analyzer has been designed particularly to flow the various standard fluids through the flow path and to flush the flow path, while minimizing any opportunity for contamination between standards, or between a standard and a blood sample. As best shown in Fig. 2, the standards are assigned to specific flow paths and chambers in septum assembly 24, and from there, the standards flow through the above-described sample flow path to waste outlet 28. The various standards and their flow paths are:
7~5 1) GA, which is a source of gas having known PO2 and PCO2 composition, connected via metering solenoid valves 46 (sold by Lee Company, Westbrook, Conn.) to a humidifier 47 and thence, via line 48 to chamber 49 of the septum assembly 24.
2) GB, which is similar to GA, having different PO2 and PCO2 composition, thereby enabling standardization of those two electrodes; GB col~municates with chamber 49 of septum assembly 24 via solenoid valves 46', humidifer 47' and line 48'.
3) pHA, a liquid of known pH that flows via line 53 to chamber 54 of septum assembly 24;
4) pHB, a standard similar to pHA, having a pH different from that o pHA, that flows via line 53' to septum assembly chamber 55. Standard pHB has a total conductivity indicative of a known equivalent hematocrit value. As explained in greater detail below, a solution having a known conductivity can be treated as the equivalent of a whole blood sample having a specific "equivalent hematocrit value."
5) EA, an electrolyte standard having a known [Na ], [K ], and [Ca ] and also having a total conductivity indicative of a known equivalent hematocrit value different from the value of pHB; EA
flows via line 56 to septum assembly chamber 57.
~?.~79S
flows via line 56 to septum assembly chamber 57.
~?.~79S
6) EB, an electrolyte standard having a known [Na ], [K ], and [Ca ], different from those of EA; standard EB
flows via line 58 to septum assembly chamber 60.
The composition of the various standard solutions is given in more detail below.
Each of lines 53, 53', 56, and 58 flows through a pinch valve 51 that is controlled by D.C. motor 63, and controller 64 to shut those lines selectively and separately when they are not in use. Each of lines 53, 53', 56, and 58 flows through a preheater to warm the standard solutions somewhat before they enter the heating block 3~. A flush line 61 bypasses pinch valve 51 and flows through preheater 52 to septum assembly chamber 62. Lines 48, 48', 61, 56, 58, 53, and 53' terminate in a rigid multi-plug connector 161 that is adapted to cooperate with the septum assembly 24 so that all of the lines can be connected simultaneously.
Specifically, connector 161 is shaped to fit within recesses of the septum assembly surrounding each inlet to a septum assembly chamber and, when connector 161 is properly positioned, an outlet from each of the lines 48, 53, 53', 56, 58, and 61 removably seals to the appropriate septum inlet by overlapping it.
A high molarity reference solution (Ref) flows through line 67 where it contacts reference electrode 34, and from there into the above sample flow path between clamp electrode 43 and waste outlet 28. The use of an open reference junction (i.e., a junction that is not enclosed in a membrane) enables the use of a low pressure flow for reference solution, and thereby reduces any possibility of contamination of the sample ~?,~ 5 flow path or the electrode sensors by reference solution. The dotted line 640indicates the region of the analyzer bathed in air from heater 66 driven by fan 65 (connected to controller 66' and fan-fail monitor 65') to stabilize temperature.
Three specific features of the analyzer are discussed below in greater detail: septum assembly 24;
electrode assembly 68 (Fig. 6); and hematocrit detection via conductivity detector 69.
C. SePtum Assembly Referring to Figs. 3, 4, 4A, and 5, removable septum assembly 24 has chambers 49, 54, 55, 57, and 60, and 62 which are separated by rubber septa 70 (Fig. 3) that have been slit to receive probe 20 and to form a seal around the probe as it is extended through the assembly. The septum assembly enabl,es the analyzer to automatically draw one or more of the reference fluids along the sample flow path without contamination of future samples. As best shown in Figs. 3, 4, 4A, and 5, the assembly includes an end mounting unit 71 and a plurality of central septa supports 72, each of which has a radial inlet 373 connecting with an axial central channel 74. A cylindrical rubber septum 70 seats in a cylindrical cavity 75 of the end mounting unit 71 and each central unit 72.
Fig. 4A shows a septum 70 in cross-section, free from the stresses it experiences in the assem~ly.
Specifically, very small (e.g. .010") annular rims 70' around the periphery of each side of septum 70 are designed so that, when the septum is seated, cavity 75 having a restrained diameter, it is subiected to moderate radial squeezing (arrow C) sealing at the ridge, so sealing is enhanced, and leakage around the ~7~s probe is reduced. In this way, the septum design provides an adequate seal without the need for a tight fit that causes friction and wear as the probe moves.
The assembly is produced by aligning all of the units with unslit septa in place, and an external sleeve 77 is then placed over the sub-assembly. The assembly then is ultrasonically welded together. After ultrasonic welding, a knife is passed through the central channels 74 to form small slits in each septum 70. Because the septa are placed in alignment first, and then slit, the size of the slits can be minimized and alignment is ensured, to reduce wear on the septa from repeated movement of the probe through them, thereby lengthening the useful life of assembly 24.
As the slits in septa 70 become worn, the seal betwe~n chambers in the assembly can be affected, and the possibility of contamination is increased, so that it is necessary to replace the septum assembly from time to time. To facilitate removal of the assembly from the analyzer, end unit 71 is designed to rotatably engage and disengage a spring-loaded latch on mounting plate 163 of analyzer 10 as shown in Fig 5. Specifically, a cylindrical recess 76 on plate 163 the face of analyzer 10 includes two thick, resilient parallel wires 373, spaced apart at a preset distance. End unit 71 of assembly 24 includes two seating posts 78 that have parallel flat sides 80 positioned to fit between wires 373. Two flanges 381 of posts 78 are generally flat, with slightly rounded corners, and define generally straight parallel grooves 82 spaced apart a distance that is very slightly less than the distance between wires 373. To insert the septum assembly, its end 71 is inserted in recess 76 in an initial position with sides .. , S
80 parallel to, and positioned between, wires 373, and then the assembly is rotated in either direction to engage wires 373 in grooves 82. At lJ8 turn, the wires are resiliently forced apart by the shoulders of grooves 82 creating a position of instability such that, a slight movement away from the 1/8 turn position will release the biasing force of the wires to re-establish a stable position. At 1/4 turn from the initial position, the wires seat in the grooves and lock the assembly in place. A 1/4 turn in either di~ection releases the assembly.
Once assembly 24 is inserted, manifold connector 161 is forced into place so that each of the various standardizing lines sealingly overlaps the proper inlet on the septum assembly as shown in Fiy. 4.
D. Electrode Assembly The fluid flow path exiting the probe communicates with an electrode assembly shown in Figs.
6-11. The path enters heating block 30 through inlet 101 (Fig. 10) and follows a circuitous route through stainless steel tubing to allow heat transfer from the heating block. Block 30 includes air detector 32 having a pair of electrodes 102 that are spaced apart in a chamber having passivated (e.g. HNO3 etched stainless steel) walls. Electrodes 102 are connected to a reflected impedance detector that is driven by an AC
source and generates a signal to be converted to digital signal to control the probe via computer 130 (Fig. 13).
From air detector 32, the fluid passes to hematocrit detector 69, described in greater detail below.
As shown in Fig. 8, the connection between heater block 30 and electrode block 80 is formed by a small piece of Tygon (TM Norton Co., Worcester, Mass.) ~9~79~;
tubing 151 that fits over the ends of stainless steel tubing from the flow path of each block; the Tygon tu~ing fits within countersinks in the respective blocks surrounding the ends of the stainless tubing. In electrode block 80, the flow path passes over each of electrodes 31, 33, 35, 37, 39, and 41 (Fig. 2) in sequence. Air detector 103 (Fig. 2), which is positioned between electrode 33 and electrode 35, operates as described above regarding detector 32. As shown in Fig. 9, the flow path follows a zig-æag path between wells at the bottom of cylindrical electrode cavities 104 in block 80.
The downstream component of the electrode assembly is a reference block 105 which includes clamp electrode 43 (Fig. 2) and a T connection upstream from it, connecting to reference line 67, allowing reference fluid ~Ref.) to be drawn out waste outlet 28. The reference electrode 34 in line 67 3erves as a reference for electrodes 35, 37, 39, and 41, (the pH, [Ca++], lK~], and ~a+] electrodes). The two gas electrodes 31 and 33 have internal references.
The flow path has a relatively narrow diameter (e.gr 0.7 mm) and is tortuous as shown in Fig. 9, and therefore clots may form in the path. Conveniently, heater block 30, electrode block 80, and reference block 105 are separate units that can be disassembled and replaced individually, as shown in Fig. 8, when it is necessary to replace one of them or to clean a blood clot from them. Specifically, heater block 30 includes a back plate 106 to which electrode block 80 is bolted, A lipped retainer 107 screws into the top edge of plate 106 and grips a notch in the top of reference block 105;
and a lip 108 on the bottom of the rear face of ~?~ 9S
reference block 105 engages a groove in the top of electrode block 80. Electrical connections to the heaters and air detectors of block 30 are made through multi-pin connector 44. Connections to the electrical components of blocks 80 and 105 are made through male connector plugs that allow easy separation of the units. A locator pin 152 extends rearwardly from plate 106 to guide the electrode assembly as it is forced in the direction of arrow B (Fig. 8) into a cooperatively shaped recess in the analyzer. A flow path inlet 109, a reference inlet 110 (Fig. 9), and waste outlet 28 extend from the assembly to be connected to tubing in the analyzer.
It is particularly advantageous that the entire fluid flow path of the electrode assembly (i.e. through the heater, the electrodes and the reference block~ can be readily removed and replaced in a short time, removing only two bolts. In that way, when a part of the flow path becomes defective, the flow path can be replaced with an alternate part and the apparatus can be restarted without taking time to cure the defect in the original part. Thus downtime on the apparatus can be significantly reduced merely by maintaining spare flow path parts.
Each of electrodes 31, 33, 35, 37, 39, and 41 is mounted on an individually replaceable unit, one of which (electrode unit 31') is shown in Fig. 11.
Electrode unit 31' consists of an electrode-carrying cylinder 89 movably inserted through an opening 83 in the back 82 of a clip 81. Clip 381 has a resiliently deflectable ridge 85 extending from one end, which terminates in a latch 86 sized to engage a groove 87 in block 80. A guide pin 88 extending from clip 3~1, at the end opposite to latch 85, fits in opening 45 in block 30. Cylinder 89 has a diameter small enough to fit easily within opening 83, and a compression spring 90 is seated between clip 81 and a flange on the cylinder, thus biasing the cylinder into an electrode cavity 104 in block 80. A flange 153 on the rear of cylinder 89 prevents the cylinder from passing through the clip opening 83. The PCO2 electrode 31 is bonded to cylinder 89, and cylinder 89 is hollow to accommodate wiring and (because it is a gas electrode with an internal reference) a reference electrode that electrically connects the electrode to signal-generating apparatus via plug 91.
E. Hematocrit Value Detector The apparatus provides a rapid, accurate hematocrit-value determination, electronically, without time~consuming, labor intensive centrifuging and visual measurement and without using a whole blood standard.
The hematocrit value determination is based on the relationship between a blood sample's electrical conductivity (C) and its hematocrit value (H),which is given the expression C = CO (1 - H) (1) where CO is the conductivity when H = O. The blood analyzer determines the conductivity of the sample by obtaining a resistance signal and comparing it to resistance signals from two reference solutions, each having a different known conductivity. The analyzer includes electrical components to provide a linear signal-to-resistivity relationship in the area of interest, so that the two references are sufficient to establish a value corresponding to the sample resistivity signal.
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The electrical conductivity of a blood sample depends on a number of factors in addition to the hematocrit value, notably concentrations of various electrolytes, so any conversion of standard fluid conductivity to hematocrit value necessarily implies concentration levels for such electrolytes. The sample electrolyte concentration may vary enough from those implied standard concentrations to require correction;
however, it has been found that, if the sodium concentration implied in the standard is used to correct the actual sample conductivity, the hematocrit value obtained will be accurate within the ranges necessary for blood hematocrit measurements.
In general, assuming a given [Na ] level and given detector geometry, the resistance (Rx) is related to hematocrit valùe as ~hown in Fig. 12A, where Ro is the resistance at H=0. Thus, Rx can be used to obtain the hematocrit value (Hx) of a blood sample using the known resistance (RA) and known hematocrit value (HA) of a standard A by the following equation:
Rx RA = Ro [1/(1 ~ ~x) ~ 1/(1 ~ HA~ (2) where Ro is the resistance at H = O.
In order to determine Ro~ a second standard having a known equivalent hematocrit value (HB) is needed. One of the pH standards, e.g. pHB, is preferably used for this purpose. By measuring the resistance (~) of pHB and the resistance (RA) of EA, Ro can be determined from equation (2). Once Ro is known, and Rx and RA can be measured, and the sample hematocrit (Hx) can be obtained by rearranging equation (2), HA being known al50 :
/(l Hx) 1/(1 - HA) ~ (Rx ~ RA)/Ro (3) ~?.9~7~5 The equivalent hematocrit values of the standards can be determined by standardizing them to actual whole blood standards.
To correct for variations in resistance attributed to variations in ~Na ~, the true sample hematocrit value (Hx*) can be obtained from Hx using the following relationship:
1/(1 - Hx*) = 1/(1 - Hx) " (Nax/NasTD) ~4) where NasTD is the [Na ] in standard EA and Nax is the sample [Na ].
When operating the analyzer, it is highly desirable to use an external control to confirm the accuracy of the instrument. The external control could be a whole blood sample having very precisely known electrolyte, pH, blood gas and hematocrit levels.
However, whole blood is relatively expensive and difficult to handle because it has a short shelf life and is relatively unstable.
For this reason, it is desirable to use a surrogate solution that mimics whole blood sufficiently to serve as a satisfactory control. A stable aqueous buffer having known electrolyte and pH could serve as a control for all readings other than hematocrit. The difficulty in using such a buffer as a hematocrit level control lies in the fact that, at normal physiological ranges, the sodium ion concentration is about 130 mM -150 mM. The conductivity of such a solution provides an equivalent hematocrit value of less than 5%, which is far below the normal range of around 50~.
It is highly desirable to have the equivalent hematocrit value of the control in normal ranges, in part because of the limitations on the linear signal-to-resistance range of the analyzer circuitry.
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One could try to raise the equivalent hematocrit level of the control by reducing its [Na+], but in so doing, the [Na ] would have to be drastically reduced and therefore the correction required by equation (4) would largely counterbalance any effective increase in the corrected hematocrit value.
This dilemma is resolved by adding an ion activity coefficient enhancer to the aqueous control solution in order to increase the ion activity measured by the [Na+] sensing electrode and to increase the resistance measured by the hematocrit resistance detector. By including such an enhancer in the control solution, the actual [Na ] may remain well below physiological levels, but the [Na+] sensing electrode measures ion activity, and the increased Na activity coefficient resulting from the presence of the enhancer will provide a signal equivalent to a physiological [Na ~; thus, the [Na ] correction resulting from equation (4) will not affect the control hematocrit significantly.
Suitable activity coefficient enhancers are polar, water-miscible organic compounds, particularly polyols such as polyethylene glycol, glycerol, and polypropylene glycol. It is possible, using such activity enhancers, to formulate control solutions with [Na ] in the normal range (130 mM - 150 mM) and with conductivities characteristic of a sample having a normal hematocrit (40% - 55%).
Suitable control solutions have a ~Nâ ] Of 20-60 mM, ~K+] of 0.5 mM - 1.7 mM, [Ca++~ of 0.1-0.5 mM, pH of 6.8-7.6 and between 10% and 50% (V/V) of an enhancer such as glycerol. Two specific such control solutions are:
~9~ 5 Control #1 Control #2 [Na+] = 52 mM [Na+] = 24 mM
[K+] = 1.5 mM [K+] = 0.7 mM
[Ca++] = 0.46 mM [Ca++] = 0.2 mM
pH = 7.46 pH = 7.46 glycerol = 38% (V/V) glycerol = 17% (V/V) Suitable pH standards are buffered solutions exemplified by the following:
pHA KH2PO4 8.695 mM
Na2HPO4 30.430 mM
NaHCO3 0.1040 mM
final pH = 7.384 pHB KH2Po4 25 mM
Na2Hpo4 25 mM
final pH = 6.840 lNa+] = 30-70 mM 950 preferred) Suitable electrolyte standards are exemplified by the following:
EA [Na+] = 120-160 mM ~140.0 preferred); ~K~]
z 4.00 mM;
~Ca++]= 1.00 mM
EB [Na+] = 75.0 mM; ~K+] = 20.0 mM;
~Ca~+]= 2.00 Suitable gas standards have between 0-25% 2 and 0-15% CO2, the balance being N2.
Suitable Ref. and flush solutions are well known to those in the art.
Referring to Fig. 12, as a solution passes through hematocrit detector 69, the resistance between electrodes 115 and 116 is measured through a reflected impedance technique in a constant current AC circuit that communicates with electrodes 115 and 116 via transforEners 120 and 121. A resistor Rl (typically about 20K ohm) is selected for stability, e.g. to avoid positive feedback due to phase shift from the boundary layer capacitance at the electrodes. The winding ratio ~-~9~
on transformer 120 is 1:1, and the winding ratio on transformer 121 is 25:1. The circuitry isolates the AC
excitation means and the measuring means from the electrodes, avoiding direct connections, d.c. polarizing ef~ects, and providing the ability to function over a relatively large common mode voltage range at the electrodes. The circuitry also provides a linear signal-to-resistivity relationship over a relatively large range.
As shown more specifically in Fig. 12, a 900 hz constant voltage A/C source 118 is connected to the drive coil of transformer 120. The other coil of transformer 120 is connected to electrode 115 of detector 69. Electrode 116 is connected through resistor Rl to the drive coil of transformer 121 to complete the loop 210 from which electrode impedance is to be communicated to the constant current AC circuit.
Transformer 121 provides feedback to maintain constant current in the impedance measuring circuit. The resulting signal from the constant circuit, reflected impedance detecting circuitry, is connected to multiplexer 183 via filtered output, full-wave rectifier 181, and non-inverting amplifier 182. The following table provides values and part numbers for the schematically illustrated components.
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Table 1 Component Value or Part No.
Rl 20K ohm R2 20K ohm R3 300K ohm R4 lM ohm Rs lOOK ohm R6 lM ohm Cl .0022 micro farad C2 10 micro farad C3 0.1 micro farad C4 0.1 micro farad Cs 0.1 micro farad Dl HLMP-1301 (Hewlett Packard) D2 HLMP-1301 (Hewlett Packard) D3 lN 821 A
Al TL074C (Texas Instrument) Transformer 120 SP-66 (Triad) Transformer 1~1 SP-48 (Triad) As also shown in Fig. 12, sodium electrode 41 and reference electrode 34 are connected to differential amplifier 190 to provide a signal representative of lNa+] to multiplexer 183. A selector 191 selects an input signal (e.g. from amplifier 190, amplifier 182, or other circuitry not shown) to be output, through filter 187 and analog-to-digital converter 188, to computer 130, an Intel SBC 80/lOB computer comprising an 8080A
CPU microprocessor.
First the standardizing solutions EA and E~
are circulated through the flow path, and computer 130 stores signals representing their respective conductivities and [Na ], as well as the HA, HB, and NasTD values. When values for RA and RB have ~,9~t;,~5 been determined, together with the known HA, HB, and NasTD values, then the corrected sample hematocrit Hx* can be derived by measuring RX and Nax, using computer 130 to perform the above calculations. A
suitable program in assembly language for performing those calculations on the 8080A CPU microprocessor is included as an appendix to this application. In the program the hematocrit value is referred to as (HCt).
III. Operation The analyzer is used to measure characteristics of a blood sample. After the apparatus is turned on, the various heaters and blowers are allowed to equilibrate and pump 29 is activated to create suction through the sample flow path and reference solution is pumped through reference line 67. In order to flush the flow path, the probe i5 retracted by drive motor 22, so that its inlet opening 21 is positioned in the flush-fluid chamber of septum assembly 24. Flush fluid therefore is drawn through the flow path and out the waste outlet 28, cleaning the flow path.
When the analyzer is idle, pump 29 is controlled to maintain a gas/liquid interface at detector 103, thereby maintaining the electrolyte and pH
electrodes in a liquid environment while maintaining the PCO2 and PO2 electrodes in a gas environment.
To standardize the electrodes the probe inlet is introduced sequentially, under the control of computer 130 and motor 22, into each septum assembly cavity; with the probe positioned in a given cavity, the computer 130 controls pinch valve motor control 64 or solenoid valves 46 and 46' to open the desired standard fluid (liquid or gas) to the septum assembly. Other standards are sealed by pinch valve Sl and solenoid ~9~l~7~
valves 46 and 46', to provide additional assurance against contamination. Standardizing with liquids EA, EB, pHA, and pHB is accomplished by flowing a standard through the flow path and then holding it there by appropriate control of pump 29 in response to liquid positions indicated by the air detectors. Standardizing with GA and GB is accomplished by flowing those standards along the flow path. Electrical signal values for each standard are recorded and stored by storage means in computer 130 for later comparison with sample signal values. Valves 46 and 46' each comprise dual solenoid valves to allow a metered flow of standardizing gas under the control of computer 130.
Standardization being complete, when analysis is required, the probe is fully extended to draw sample solution through the flow path, without contamination from standards. Signals representative of each measured ~ample characteristic are generated and transferred to computer 130 for comparison with standard signals thus establishing a value for each characteristic that is fed to output apparatus--i.e., C.R.T. display 12 and tape printout 14. With the exception of the hematocrit measurement, the details of the apparatus for generating standard and sample signals, for comparing those signals, and for calculating values for sample characteristics are well known and need not be repeated here.
Fig. 13 shows other aspects of the electronic components and their connection to computer 130.
Specifically, in Fig. 13, inputs to computer 130 are provided from keypad 16 and from multiplexer 183 via filter 187 and A/D converter 188. The computer provides output to probe motor control 222, pinch valve motor ~?,917~5 controller 64, sample preheater controller 160', air heater and blower controller 66', and solenoid valves 46 and 46'. Also, computer 130 provides output to CRT
screen 12 and printer 14.
Other Embodiments Other embodiments are within the following claim. For example, other blood components or additional blood components can be sensed by the analyzer. Other electrolytes such as [Cl ] can be used as a surrogate for hematocrit. In that case, suitable [Cl ] concentrations of standardizing solutions EA and EB are 110 mM and 60 mM, respectively. In that case, 41 in Fig. 12A would be a [Cl ] sensing electrode. In place of the electrode isolating circuitry described above, the electrodes could be directly coupled to an AC conductivity measuring circuit with a local ground ~e.g. in the preheater).
flows via line 58 to septum assembly chamber 60.
The composition of the various standard solutions is given in more detail below.
Each of lines 53, 53', 56, and 58 flows through a pinch valve 51 that is controlled by D.C. motor 63, and controller 64 to shut those lines selectively and separately when they are not in use. Each of lines 53, 53', 56, and 58 flows through a preheater to warm the standard solutions somewhat before they enter the heating block 3~. A flush line 61 bypasses pinch valve 51 and flows through preheater 52 to septum assembly chamber 62. Lines 48, 48', 61, 56, 58, 53, and 53' terminate in a rigid multi-plug connector 161 that is adapted to cooperate with the septum assembly 24 so that all of the lines can be connected simultaneously.
Specifically, connector 161 is shaped to fit within recesses of the septum assembly surrounding each inlet to a septum assembly chamber and, when connector 161 is properly positioned, an outlet from each of the lines 48, 53, 53', 56, 58, and 61 removably seals to the appropriate septum inlet by overlapping it.
A high molarity reference solution (Ref) flows through line 67 where it contacts reference electrode 34, and from there into the above sample flow path between clamp electrode 43 and waste outlet 28. The use of an open reference junction (i.e., a junction that is not enclosed in a membrane) enables the use of a low pressure flow for reference solution, and thereby reduces any possibility of contamination of the sample ~?,~ 5 flow path or the electrode sensors by reference solution. The dotted line 640indicates the region of the analyzer bathed in air from heater 66 driven by fan 65 (connected to controller 66' and fan-fail monitor 65') to stabilize temperature.
Three specific features of the analyzer are discussed below in greater detail: septum assembly 24;
electrode assembly 68 (Fig. 6); and hematocrit detection via conductivity detector 69.
C. SePtum Assembly Referring to Figs. 3, 4, 4A, and 5, removable septum assembly 24 has chambers 49, 54, 55, 57, and 60, and 62 which are separated by rubber septa 70 (Fig. 3) that have been slit to receive probe 20 and to form a seal around the probe as it is extended through the assembly. The septum assembly enabl,es the analyzer to automatically draw one or more of the reference fluids along the sample flow path without contamination of future samples. As best shown in Figs. 3, 4, 4A, and 5, the assembly includes an end mounting unit 71 and a plurality of central septa supports 72, each of which has a radial inlet 373 connecting with an axial central channel 74. A cylindrical rubber septum 70 seats in a cylindrical cavity 75 of the end mounting unit 71 and each central unit 72.
Fig. 4A shows a septum 70 in cross-section, free from the stresses it experiences in the assem~ly.
Specifically, very small (e.g. .010") annular rims 70' around the periphery of each side of septum 70 are designed so that, when the septum is seated, cavity 75 having a restrained diameter, it is subiected to moderate radial squeezing (arrow C) sealing at the ridge, so sealing is enhanced, and leakage around the ~7~s probe is reduced. In this way, the septum design provides an adequate seal without the need for a tight fit that causes friction and wear as the probe moves.
The assembly is produced by aligning all of the units with unslit septa in place, and an external sleeve 77 is then placed over the sub-assembly. The assembly then is ultrasonically welded together. After ultrasonic welding, a knife is passed through the central channels 74 to form small slits in each septum 70. Because the septa are placed in alignment first, and then slit, the size of the slits can be minimized and alignment is ensured, to reduce wear on the septa from repeated movement of the probe through them, thereby lengthening the useful life of assembly 24.
As the slits in septa 70 become worn, the seal betwe~n chambers in the assembly can be affected, and the possibility of contamination is increased, so that it is necessary to replace the septum assembly from time to time. To facilitate removal of the assembly from the analyzer, end unit 71 is designed to rotatably engage and disengage a spring-loaded latch on mounting plate 163 of analyzer 10 as shown in Fig 5. Specifically, a cylindrical recess 76 on plate 163 the face of analyzer 10 includes two thick, resilient parallel wires 373, spaced apart at a preset distance. End unit 71 of assembly 24 includes two seating posts 78 that have parallel flat sides 80 positioned to fit between wires 373. Two flanges 381 of posts 78 are generally flat, with slightly rounded corners, and define generally straight parallel grooves 82 spaced apart a distance that is very slightly less than the distance between wires 373. To insert the septum assembly, its end 71 is inserted in recess 76 in an initial position with sides .. , S
80 parallel to, and positioned between, wires 373, and then the assembly is rotated in either direction to engage wires 373 in grooves 82. At lJ8 turn, the wires are resiliently forced apart by the shoulders of grooves 82 creating a position of instability such that, a slight movement away from the 1/8 turn position will release the biasing force of the wires to re-establish a stable position. At 1/4 turn from the initial position, the wires seat in the grooves and lock the assembly in place. A 1/4 turn in either di~ection releases the assembly.
Once assembly 24 is inserted, manifold connector 161 is forced into place so that each of the various standardizing lines sealingly overlaps the proper inlet on the septum assembly as shown in Fiy. 4.
D. Electrode Assembly The fluid flow path exiting the probe communicates with an electrode assembly shown in Figs.
6-11. The path enters heating block 30 through inlet 101 (Fig. 10) and follows a circuitous route through stainless steel tubing to allow heat transfer from the heating block. Block 30 includes air detector 32 having a pair of electrodes 102 that are spaced apart in a chamber having passivated (e.g. HNO3 etched stainless steel) walls. Electrodes 102 are connected to a reflected impedance detector that is driven by an AC
source and generates a signal to be converted to digital signal to control the probe via computer 130 (Fig. 13).
From air detector 32, the fluid passes to hematocrit detector 69, described in greater detail below.
As shown in Fig. 8, the connection between heater block 30 and electrode block 80 is formed by a small piece of Tygon (TM Norton Co., Worcester, Mass.) ~9~79~;
tubing 151 that fits over the ends of stainless steel tubing from the flow path of each block; the Tygon tu~ing fits within countersinks in the respective blocks surrounding the ends of the stainless tubing. In electrode block 80, the flow path passes over each of electrodes 31, 33, 35, 37, 39, and 41 (Fig. 2) in sequence. Air detector 103 (Fig. 2), which is positioned between electrode 33 and electrode 35, operates as described above regarding detector 32. As shown in Fig. 9, the flow path follows a zig-æag path between wells at the bottom of cylindrical electrode cavities 104 in block 80.
The downstream component of the electrode assembly is a reference block 105 which includes clamp electrode 43 (Fig. 2) and a T connection upstream from it, connecting to reference line 67, allowing reference fluid ~Ref.) to be drawn out waste outlet 28. The reference electrode 34 in line 67 3erves as a reference for electrodes 35, 37, 39, and 41, (the pH, [Ca++], lK~], and ~a+] electrodes). The two gas electrodes 31 and 33 have internal references.
The flow path has a relatively narrow diameter (e.gr 0.7 mm) and is tortuous as shown in Fig. 9, and therefore clots may form in the path. Conveniently, heater block 30, electrode block 80, and reference block 105 are separate units that can be disassembled and replaced individually, as shown in Fig. 8, when it is necessary to replace one of them or to clean a blood clot from them. Specifically, heater block 30 includes a back plate 106 to which electrode block 80 is bolted, A lipped retainer 107 screws into the top edge of plate 106 and grips a notch in the top of reference block 105;
and a lip 108 on the bottom of the rear face of ~?~ 9S
reference block 105 engages a groove in the top of electrode block 80. Electrical connections to the heaters and air detectors of block 30 are made through multi-pin connector 44. Connections to the electrical components of blocks 80 and 105 are made through male connector plugs that allow easy separation of the units. A locator pin 152 extends rearwardly from plate 106 to guide the electrode assembly as it is forced in the direction of arrow B (Fig. 8) into a cooperatively shaped recess in the analyzer. A flow path inlet 109, a reference inlet 110 (Fig. 9), and waste outlet 28 extend from the assembly to be connected to tubing in the analyzer.
It is particularly advantageous that the entire fluid flow path of the electrode assembly (i.e. through the heater, the electrodes and the reference block~ can be readily removed and replaced in a short time, removing only two bolts. In that way, when a part of the flow path becomes defective, the flow path can be replaced with an alternate part and the apparatus can be restarted without taking time to cure the defect in the original part. Thus downtime on the apparatus can be significantly reduced merely by maintaining spare flow path parts.
Each of electrodes 31, 33, 35, 37, 39, and 41 is mounted on an individually replaceable unit, one of which (electrode unit 31') is shown in Fig. 11.
Electrode unit 31' consists of an electrode-carrying cylinder 89 movably inserted through an opening 83 in the back 82 of a clip 81. Clip 381 has a resiliently deflectable ridge 85 extending from one end, which terminates in a latch 86 sized to engage a groove 87 in block 80. A guide pin 88 extending from clip 3~1, at the end opposite to latch 85, fits in opening 45 in block 30. Cylinder 89 has a diameter small enough to fit easily within opening 83, and a compression spring 90 is seated between clip 81 and a flange on the cylinder, thus biasing the cylinder into an electrode cavity 104 in block 80. A flange 153 on the rear of cylinder 89 prevents the cylinder from passing through the clip opening 83. The PCO2 electrode 31 is bonded to cylinder 89, and cylinder 89 is hollow to accommodate wiring and (because it is a gas electrode with an internal reference) a reference electrode that electrically connects the electrode to signal-generating apparatus via plug 91.
E. Hematocrit Value Detector The apparatus provides a rapid, accurate hematocrit-value determination, electronically, without time~consuming, labor intensive centrifuging and visual measurement and without using a whole blood standard.
The hematocrit value determination is based on the relationship between a blood sample's electrical conductivity (C) and its hematocrit value (H),which is given the expression C = CO (1 - H) (1) where CO is the conductivity when H = O. The blood analyzer determines the conductivity of the sample by obtaining a resistance signal and comparing it to resistance signals from two reference solutions, each having a different known conductivity. The analyzer includes electrical components to provide a linear signal-to-resistivity relationship in the area of interest, so that the two references are sufficient to establish a value corresponding to the sample resistivity signal.
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The electrical conductivity of a blood sample depends on a number of factors in addition to the hematocrit value, notably concentrations of various electrolytes, so any conversion of standard fluid conductivity to hematocrit value necessarily implies concentration levels for such electrolytes. The sample electrolyte concentration may vary enough from those implied standard concentrations to require correction;
however, it has been found that, if the sodium concentration implied in the standard is used to correct the actual sample conductivity, the hematocrit value obtained will be accurate within the ranges necessary for blood hematocrit measurements.
In general, assuming a given [Na ] level and given detector geometry, the resistance (Rx) is related to hematocrit valùe as ~hown in Fig. 12A, where Ro is the resistance at H=0. Thus, Rx can be used to obtain the hematocrit value (Hx) of a blood sample using the known resistance (RA) and known hematocrit value (HA) of a standard A by the following equation:
Rx RA = Ro [1/(1 ~ ~x) ~ 1/(1 ~ HA~ (2) where Ro is the resistance at H = O.
In order to determine Ro~ a second standard having a known equivalent hematocrit value (HB) is needed. One of the pH standards, e.g. pHB, is preferably used for this purpose. By measuring the resistance (~) of pHB and the resistance (RA) of EA, Ro can be determined from equation (2). Once Ro is known, and Rx and RA can be measured, and the sample hematocrit (Hx) can be obtained by rearranging equation (2), HA being known al50 :
/(l Hx) 1/(1 - HA) ~ (Rx ~ RA)/Ro (3) ~?.9~7~5 The equivalent hematocrit values of the standards can be determined by standardizing them to actual whole blood standards.
To correct for variations in resistance attributed to variations in ~Na ~, the true sample hematocrit value (Hx*) can be obtained from Hx using the following relationship:
1/(1 - Hx*) = 1/(1 - Hx) " (Nax/NasTD) ~4) where NasTD is the [Na ] in standard EA and Nax is the sample [Na ].
When operating the analyzer, it is highly desirable to use an external control to confirm the accuracy of the instrument. The external control could be a whole blood sample having very precisely known electrolyte, pH, blood gas and hematocrit levels.
However, whole blood is relatively expensive and difficult to handle because it has a short shelf life and is relatively unstable.
For this reason, it is desirable to use a surrogate solution that mimics whole blood sufficiently to serve as a satisfactory control. A stable aqueous buffer having known electrolyte and pH could serve as a control for all readings other than hematocrit. The difficulty in using such a buffer as a hematocrit level control lies in the fact that, at normal physiological ranges, the sodium ion concentration is about 130 mM -150 mM. The conductivity of such a solution provides an equivalent hematocrit value of less than 5%, which is far below the normal range of around 50~.
It is highly desirable to have the equivalent hematocrit value of the control in normal ranges, in part because of the limitations on the linear signal-to-resistance range of the analyzer circuitry.
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One could try to raise the equivalent hematocrit level of the control by reducing its [Na+], but in so doing, the [Na ] would have to be drastically reduced and therefore the correction required by equation (4) would largely counterbalance any effective increase in the corrected hematocrit value.
This dilemma is resolved by adding an ion activity coefficient enhancer to the aqueous control solution in order to increase the ion activity measured by the [Na+] sensing electrode and to increase the resistance measured by the hematocrit resistance detector. By including such an enhancer in the control solution, the actual [Na ] may remain well below physiological levels, but the [Na+] sensing electrode measures ion activity, and the increased Na activity coefficient resulting from the presence of the enhancer will provide a signal equivalent to a physiological [Na ~; thus, the [Na ] correction resulting from equation (4) will not affect the control hematocrit significantly.
Suitable activity coefficient enhancers are polar, water-miscible organic compounds, particularly polyols such as polyethylene glycol, glycerol, and polypropylene glycol. It is possible, using such activity enhancers, to formulate control solutions with [Na ] in the normal range (130 mM - 150 mM) and with conductivities characteristic of a sample having a normal hematocrit (40% - 55%).
Suitable control solutions have a ~Nâ ] Of 20-60 mM, ~K+] of 0.5 mM - 1.7 mM, [Ca++~ of 0.1-0.5 mM, pH of 6.8-7.6 and between 10% and 50% (V/V) of an enhancer such as glycerol. Two specific such control solutions are:
~9~ 5 Control #1 Control #2 [Na+] = 52 mM [Na+] = 24 mM
[K+] = 1.5 mM [K+] = 0.7 mM
[Ca++] = 0.46 mM [Ca++] = 0.2 mM
pH = 7.46 pH = 7.46 glycerol = 38% (V/V) glycerol = 17% (V/V) Suitable pH standards are buffered solutions exemplified by the following:
pHA KH2PO4 8.695 mM
Na2HPO4 30.430 mM
NaHCO3 0.1040 mM
final pH = 7.384 pHB KH2Po4 25 mM
Na2Hpo4 25 mM
final pH = 6.840 lNa+] = 30-70 mM 950 preferred) Suitable electrolyte standards are exemplified by the following:
EA [Na+] = 120-160 mM ~140.0 preferred); ~K~]
z 4.00 mM;
~Ca++]= 1.00 mM
EB [Na+] = 75.0 mM; ~K+] = 20.0 mM;
~Ca~+]= 2.00 Suitable gas standards have between 0-25% 2 and 0-15% CO2, the balance being N2.
Suitable Ref. and flush solutions are well known to those in the art.
Referring to Fig. 12, as a solution passes through hematocrit detector 69, the resistance between electrodes 115 and 116 is measured through a reflected impedance technique in a constant current AC circuit that communicates with electrodes 115 and 116 via transforEners 120 and 121. A resistor Rl (typically about 20K ohm) is selected for stability, e.g. to avoid positive feedback due to phase shift from the boundary layer capacitance at the electrodes. The winding ratio ~-~9~
on transformer 120 is 1:1, and the winding ratio on transformer 121 is 25:1. The circuitry isolates the AC
excitation means and the measuring means from the electrodes, avoiding direct connections, d.c. polarizing ef~ects, and providing the ability to function over a relatively large common mode voltage range at the electrodes. The circuitry also provides a linear signal-to-resistivity relationship over a relatively large range.
As shown more specifically in Fig. 12, a 900 hz constant voltage A/C source 118 is connected to the drive coil of transformer 120. The other coil of transformer 120 is connected to electrode 115 of detector 69. Electrode 116 is connected through resistor Rl to the drive coil of transformer 121 to complete the loop 210 from which electrode impedance is to be communicated to the constant current AC circuit.
Transformer 121 provides feedback to maintain constant current in the impedance measuring circuit. The resulting signal from the constant circuit, reflected impedance detecting circuitry, is connected to multiplexer 183 via filtered output, full-wave rectifier 181, and non-inverting amplifier 182. The following table provides values and part numbers for the schematically illustrated components.
91~9S
Table 1 Component Value or Part No.
Rl 20K ohm R2 20K ohm R3 300K ohm R4 lM ohm Rs lOOK ohm R6 lM ohm Cl .0022 micro farad C2 10 micro farad C3 0.1 micro farad C4 0.1 micro farad Cs 0.1 micro farad Dl HLMP-1301 (Hewlett Packard) D2 HLMP-1301 (Hewlett Packard) D3 lN 821 A
Al TL074C (Texas Instrument) Transformer 120 SP-66 (Triad) Transformer 1~1 SP-48 (Triad) As also shown in Fig. 12, sodium electrode 41 and reference electrode 34 are connected to differential amplifier 190 to provide a signal representative of lNa+] to multiplexer 183. A selector 191 selects an input signal (e.g. from amplifier 190, amplifier 182, or other circuitry not shown) to be output, through filter 187 and analog-to-digital converter 188, to computer 130, an Intel SBC 80/lOB computer comprising an 8080A
CPU microprocessor.
First the standardizing solutions EA and E~
are circulated through the flow path, and computer 130 stores signals representing their respective conductivities and [Na ], as well as the HA, HB, and NasTD values. When values for RA and RB have ~,9~t;,~5 been determined, together with the known HA, HB, and NasTD values, then the corrected sample hematocrit Hx* can be derived by measuring RX and Nax, using computer 130 to perform the above calculations. A
suitable program in assembly language for performing those calculations on the 8080A CPU microprocessor is included as an appendix to this application. In the program the hematocrit value is referred to as (HCt).
III. Operation The analyzer is used to measure characteristics of a blood sample. After the apparatus is turned on, the various heaters and blowers are allowed to equilibrate and pump 29 is activated to create suction through the sample flow path and reference solution is pumped through reference line 67. In order to flush the flow path, the probe i5 retracted by drive motor 22, so that its inlet opening 21 is positioned in the flush-fluid chamber of septum assembly 24. Flush fluid therefore is drawn through the flow path and out the waste outlet 28, cleaning the flow path.
When the analyzer is idle, pump 29 is controlled to maintain a gas/liquid interface at detector 103, thereby maintaining the electrolyte and pH
electrodes in a liquid environment while maintaining the PCO2 and PO2 electrodes in a gas environment.
To standardize the electrodes the probe inlet is introduced sequentially, under the control of computer 130 and motor 22, into each septum assembly cavity; with the probe positioned in a given cavity, the computer 130 controls pinch valve motor control 64 or solenoid valves 46 and 46' to open the desired standard fluid (liquid or gas) to the septum assembly. Other standards are sealed by pinch valve Sl and solenoid ~9~l~7~
valves 46 and 46', to provide additional assurance against contamination. Standardizing with liquids EA, EB, pHA, and pHB is accomplished by flowing a standard through the flow path and then holding it there by appropriate control of pump 29 in response to liquid positions indicated by the air detectors. Standardizing with GA and GB is accomplished by flowing those standards along the flow path. Electrical signal values for each standard are recorded and stored by storage means in computer 130 for later comparison with sample signal values. Valves 46 and 46' each comprise dual solenoid valves to allow a metered flow of standardizing gas under the control of computer 130.
Standardization being complete, when analysis is required, the probe is fully extended to draw sample solution through the flow path, without contamination from standards. Signals representative of each measured ~ample characteristic are generated and transferred to computer 130 for comparison with standard signals thus establishing a value for each characteristic that is fed to output apparatus--i.e., C.R.T. display 12 and tape printout 14. With the exception of the hematocrit measurement, the details of the apparatus for generating standard and sample signals, for comparing those signals, and for calculating values for sample characteristics are well known and need not be repeated here.
Fig. 13 shows other aspects of the electronic components and their connection to computer 130.
Specifically, in Fig. 13, inputs to computer 130 are provided from keypad 16 and from multiplexer 183 via filter 187 and A/D converter 188. The computer provides output to probe motor control 222, pinch valve motor ~?,917~5 controller 64, sample preheater controller 160', air heater and blower controller 66', and solenoid valves 46 and 46'. Also, computer 130 provides output to CRT
screen 12 and printer 14.
Other Embodiments Other embodiments are within the following claim. For example, other blood components or additional blood components can be sensed by the analyzer. Other electrolytes such as [Cl ] can be used as a surrogate for hematocrit. In that case, suitable [Cl ] concentrations of standardizing solutions EA and EB are 110 mM and 60 mM, respectively. In that case, 41 in Fig. 12A would be a [Cl ] sensing electrode. In place of the electrode isolating circuitry described above, the electrodes could be directly coupled to an AC conductivity measuring circuit with a local ground ~e.g. in the preheater).
Claims (22)
1. A method for determining the hematocrit value of a blood sample by:
a) providing apparatus comprising a liquid flow path, means in the flow path for generating an electrical signal representative of the electrical conductivity of liquid in the path, and means in the flow path for obtaining an electrical signal representative of the concentration of at least one ion species in liquid in the flow path;
b) introducing standardizing solution in the flow path having a known concentration of said ion species and having a conductivity indicative of a known equivalent hematocrit value, and obtaining a signal representative of said standardizing solution conductivity and obtaining a signal representative of said known ion species concentration;
c) either before or after introducing the standardizing solution, introducing the sample in the flow path and obtaining an electric signal representative of the sample conductivity and an electric signal representative of the sample ion-species concentration; and d) deriving a tentative sample hematocrit value responsive to the sample conductivity signal, with reference to said standardizing conductivity signal and to said known standardizing equivalent hematocrit value;
and e) correcting said tentative sample hematocrit value with reference to said sample and standardizing ion concentration signals and to said known ion concentration value.
a) providing apparatus comprising a liquid flow path, means in the flow path for generating an electrical signal representative of the electrical conductivity of liquid in the path, and means in the flow path for obtaining an electrical signal representative of the concentration of at least one ion species in liquid in the flow path;
b) introducing standardizing solution in the flow path having a known concentration of said ion species and having a conductivity indicative of a known equivalent hematocrit value, and obtaining a signal representative of said standardizing solution conductivity and obtaining a signal representative of said known ion species concentration;
c) either before or after introducing the standardizing solution, introducing the sample in the flow path and obtaining an electric signal representative of the sample conductivity and an electric signal representative of the sample ion-species concentration; and d) deriving a tentative sample hematocrit value responsive to the sample conductivity signal, with reference to said standardizing conductivity signal and to said known standardizing equivalent hematocrit value;
and e) correcting said tentative sample hematocrit value with reference to said sample and standardizing ion concentration signals and to said known ion concentration value.
2. The method of claim 1 wherein said method further comprises providing, from time to time, an external validation of said apparatus by introducing a control solution in said flow path, said control solution having a known ion species concentration, and a conductivity representative of a known equivalent hematocrit level.
3. The method of claim 2 wherein said control solution equivalent hematocrit level is within a physiologically normal range, and said control solution ion species concentration is within a physiologically normal range.
4. The method of claim 2 wherein said control solution comprises an ion activity enhancing agent.
5. The method of claim 2 wherein said agent is a polyol.
6. The method of claim 5 wherein said polyol is selected from glycerol and polyalkyl glycols.
7. The method of claim 1 or claim 2 wherein said conductivity obtaining step comprises:
a) providing electrodes in said flow path coupled to a constant current AC circuit via a transformer;
b) applying an AC signal to said electrodes from said circuit via said transformer; and c) detecting impedance reflected in said AC
circuit.
a) providing electrodes in said flow path coupled to a constant current AC circuit via a transformer;
b) applying an AC signal to said electrodes from said circuit via said transformer; and c) detecting impedance reflected in said AC
circuit.
8. The method of claim 1 or claim 2 wherein said method comprises performing the following steps in any order:
a) obtaining said electrical signals representative of standardizing conductivity and standardizing ion concentration;
b) storing signals representative of said known standardizing equivalent hematocrit value and said known standardizing ion concentration value;
c) obtaining said electrical signals representative of sample ion concentration and standardizing ion concentration;
d) comparing said sample and said standardizing ion concentration signals with reference to said stored known standardizing concentration value signal to derive a signal representative of sample ion concentration value;
e) comparing said sample and said standardizing conductivity signals with reference to said stored standardizing hematocrit value signal to derive a signal representative of a tentative sample hematocrit value;
f) correcting said tentative sample hematocrit value signal with reference to said sample ion concentration signal and said stored standardizing ion concentration value signal.
a) obtaining said electrical signals representative of standardizing conductivity and standardizing ion concentration;
b) storing signals representative of said known standardizing equivalent hematocrit value and said known standardizing ion concentration value;
c) obtaining said electrical signals representative of sample ion concentration and standardizing ion concentration;
d) comparing said sample and said standardizing ion concentration signals with reference to said stored known standardizing concentration value signal to derive a signal representative of sample ion concentration value;
e) comparing said sample and said standardizing conductivity signals with reference to said stored standardizing hematocrit value signal to derive a signal representative of a tentative sample hematocrit value;
f) correcting said tentative sample hematocrit value signal with reference to said sample ion concentration signal and said stored standardizing ion concentration value signal.
9. The method of either claim 1 or claim 2 wherein said ion species is Na+ or Cl-.
10. Apparatus for determining hematocrit value in a blood sample comprising: 1) means for providing a fluid flow path; 2) means in said flow path for providing an electrical signal representative of the conductivity of liquid passing along said flow path; 3) means in said flow path for providing a signal representative of the concentration of an ion species in liquid passing along said flow path; 4) means for introducing said blood sample into said flow path to obtain a signal representative of sample conductivity and of sample ion species concentration; 5) means for introducing into said flow path a standardizing solution having a known concentration of an ion species and having a conductivity representative of a known equivalent hematocrit value; 6) means for deriving a signal representative of a tentative sample hematocrit value from the sample conductivity signal, with reference to the standardizing conductivity signal and to the standardizing equivalent hematocrit value; and 7) means for correcting said tentative sample hematocrit value with reference to said standardizing and sample ion concentration signals and to said known standardizing ion concentration.
11. The apparatus of claim 10 wherein said apparatus comprises means for storing either said sample or said standardizing conductivity signal, and means for comparing said conductivity signals with reference to said known standardizing equivalent hematocrit value to generate a signal representative of said tentative sample hematocrit value.
12. The apparatus of claim 11 wherein said means for correcting said tentative sample hematocrit value signal comprises means for storing either said standardizing or said sample ion concentration signal and comparing said concentration signals with reference to said known standardizing ion concentration value.
13. The apparatus of claim 10 wherein said apparatus comprises at least two standardizing solutions, each of which has a conductivity indicative of a known equivalent hematocrit value and a known ion concentration.
14. The apparatus of claim 10 wherein said ion species is Na+ or Cl-.
15. The apparatus of claim 10 wherein said conductivity measuring means comprises electrodes in said flow path, a constant current AC circuit coupled to said electrodes via a transformer, and means for detecting reflected impedance in said AC circuit.
16. The apparatus of claim 15 wherein said conductivity signal-generating means comprises: 1) a first transformer for coupling said AC circuit to said electrodes; 2) a second transformer for maintaining constant current in said AC circuit; and 3) means establishing a loop, connected between said electrodes, comprising means connected in said loop between said electrodes and said second transformer to compensate for inherent capacitance at the electrode/sample interface.
17. The apparatus of claim 16 wherein said apparatus comprises an ion-species sensitive electrode positioned in said flow path and connected via an electrical circuit to the input of a multiplexer, said impedance detecting means also being connected to the input of said multiplexer, said multiplexer having an output means connected via an analog-to-digital converter to a means for storing and comparing signals, and to said means for correcting sample conductivity.
18. A control solution kit for evaluating apparatus that determines a tentative level for the hematocrit of a blood sample by determining the sample conductivity and correcting said tentative level with reference to a sample ion species concentration level, said kit comprising an aqueous solution comprising said ion species and an ion activity enhancing agent, said solution having a known concentration of said ion and a known equivalent hematocrit value.
19. The kit of claim 18 wherein said ion species is Na+ or Cl-.
20. The kit of claim 19 wherein said agent is a polyol.
21. The kit of claim 19 wherein said polyol is selected from glycerol and polyalkyl glycols.
22. The kit of claim 18 wherein said ion concentration and said equivalent hematocrit level are within physiologically normal ranges.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US757,573 | 1985-07-22 | ||
| US06/757,573 US4686479A (en) | 1985-07-22 | 1985-07-22 | Apparatus and control kit for analyzing blood sample values including hematocrit |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1291795C true CA1291795C (en) | 1991-11-05 |
Family
ID=25048351
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000514031A Expired - Lifetime CA1291795C (en) | 1985-07-22 | 1986-07-17 | Blood analyzer |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US4686479A (en) |
| EP (1) | EP0213343B2 (en) |
| JP (2) | JPH0827278B2 (en) |
| AT (1) | ATE58968T1 (en) |
| CA (1) | CA1291795C (en) |
| DE (1) | DE3676011D1 (en) |
| DK (1) | DK172264B1 (en) |
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-
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- 1985-07-22 US US06/757,573 patent/US4686479A/en not_active Expired - Lifetime
-
1986
- 1986-07-14 EP EP86109615A patent/EP0213343B2/en not_active Expired - Lifetime
- 1986-07-14 DE DE8686109615T patent/DE3676011D1/en not_active Expired - Fee Related
- 1986-07-14 AT AT86109615T patent/ATE58968T1/en not_active IP Right Cessation
- 1986-07-17 CA CA000514031A patent/CA1291795C/en not_active Expired - Lifetime
- 1986-07-21 DK DK344986A patent/DK172264B1/en not_active IP Right Cessation
- 1986-07-22 JP JP61172690A patent/JPH0827278B2/en not_active Expired - Fee Related
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1995
- 1995-08-04 JP JP7230659A patent/JP2954508B2/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| DE3676011D1 (en) | 1991-01-17 |
| DK344986D0 (en) | 1986-07-21 |
| DK344986A (en) | 1987-01-23 |
| JPS6225262A (en) | 1987-02-03 |
| JP2954508B2 (en) | 1999-09-27 |
| EP0213343B2 (en) | 1995-02-01 |
| EP0213343A3 (en) | 1987-12-09 |
| JPH08178918A (en) | 1996-07-12 |
| JPH0827278B2 (en) | 1996-03-21 |
| DK172264B1 (en) | 1998-02-09 |
| ATE58968T1 (en) | 1990-12-15 |
| EP0213343B1 (en) | 1990-12-05 |
| US4686479A (en) | 1987-08-11 |
| EP0213343A2 (en) | 1987-03-11 |
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