WO1981002218A1 - Electrodes de selection d'ions et procede d'etalonnage de celles-ci - Google Patents

Electrodes de selection d'ions et procede d'etalonnage de celles-ci Download PDF

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Publication number
WO1981002218A1
WO1981002218A1 PCT/US1981/000049 US8100049W WO8102218A1 WO 1981002218 A1 WO1981002218 A1 WO 1981002218A1 US 8100049 W US8100049 W US 8100049W WO 8102218 A1 WO8102218 A1 WO 8102218A1
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Prior art keywords
invention defined
electrode
ion
half cell
electrodes
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Application number
PCT/US1981/000049
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English (en)
Inventor
J Kater
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J Kater
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Publication date
Application filed by J Kater filed Critical J Kater
Priority to DE8181900665T priority Critical patent/DE3171358D1/de
Priority to AT81900665T priority patent/ATE14352T1/de
Publication of WO1981002218A1 publication Critical patent/WO1981002218A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14542—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring blood gases
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1473—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means invasive, e.g. introduced into the body by a catheter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1495—Calibrating or testing of in-vivo probes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3607—Regulation parameters
    • A61M1/3609—Physical characteristics of the blood, e.g. haematocrit, urea
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/333—Ion-selective electrodes or membranes
    • G01N27/3335—Ion-selective electrodes or membranes the membrane containing at least one organic component

Definitions

  • This invention relates to improvements in ion -selective electrodes and reference electrodes, and it relates in particular to structures and materials and techniques to be employed in producing such electrodes and in using them.
  • labora ⁇ tory data should be available rapidly and, preferably, con ⁇ tinuously.
  • Blood electrolytes such as potassium, sodium, calcium and chloride are important elements. Of particular importance is the ability to measure ionized potassium con- tinuously (in vito) or at least rapidly (in vitro) to pro ⁇ vide real-time data to the physician.
  • the gradient of po ⁇ tassium across the cell membrane is the principal contri ⁇ butor to the membrane potential. Maintenance of this elec ⁇ trical potential is essential for normal function of all nervous and muscular tissue, including the conducting and contracting elements of the heart.
  • the continuous or rapid measurement of potassium ion is important in intensive care, postcardiopulmonary by-pass, cardioplegia, and administrati of digitalis and diuretics, acute yocardial infarction, re failure and the treatment of burn patients and diabetic patients.
  • a thin, catheter-mounted potassium electrode is commercially available.
  • Electrodes containing a liquid electrolyte can become a hazard to the patient should the sensing membrane, separating the electrolyte from the patient's blood, burst.
  • liquid filled electrodes cannot be sterilized by accepted sterilization procedures, such as ethylene oxide treatment, autoclaving and gamma radiation. These accepted steriliza ⁇ tion procedures render such liquid filled electrodes in ⁇ operative by one or a combination of: 1) physical damage to the ion sensitive membrane;
  • the reference electrode includes a body of electrolyte and a half cell. Instead of a selective membrane, it includes a "salt bridge," but like the selective electrode, it has been large and cumbersome. In some applications requiring a miniaturized selective electrode, it matters little if the reference electrode is large, but in other application there is a need for a miniaturized reference electrode. In still other applications there is need for a miniaturiz reference device even if the selective electrode is not small.
  • a means for con ⁇ taining a layer of liquid in immobilized form between an ion selective membrane and the half cell segment of the electrical path.
  • That means may comprise, and in preferred form does comprise, a membrane or layer of hydrophilic material interposed between the sensitive membrane and the half cell.
  • An electrolyte is contained in the hydrophilic layer. The electrolyte may be trapped in place by the ion selective membrane during the manufacturing process or, if preferred, in a given application the electrolytic layer may be formed by the hydration of a hydrophilic layer and the selective membrane, as the sensor is soaked in prepara- tion for use or at the point of manufacture.
  • the electrode can be repeatedly ethylene oxide or gamma radiation sterilized without effecting the stability or performance of the electrode;
  • the electrode may be stored wet or dry.
  • Electrodes with a tip diameter of 0.75 mm have been fabricated, with a rigid of flexible shaft ranging in length from 2 cm to 60 cm.
  • the invention extends to the use of particular preferred materials and preferred structural forms and pre ⁇ ferred production methods which are described below in con- nection with the description of the best mode know to application for practicing the invention.
  • the invention also provides a novel method for using miniature ion selective electrodes, and in this con- nection, it provides a new, miniature reference electrode and a new combination electrode.
  • the preferred form of the method utilizes a two-channel direct reading analyzer for continuous inter- and intravascular monitoring of blood electrolytes also presents a calibration problem. Elec ⁇ trodes placed in a blood vessel (intervascular) or in a by ⁇ pass loop (extravascular) cannot be taken out and replaced for calibration or a calibration check during surgery or in the intensive care ward. Such a method would be time con ⁇ suming,- traumatic, and create a potential for bacterial contamination, even if the calibrating solutions were sterilized. To solve these problems, an in vivo or in-line calibration method is employed using a dual channel analyzer as follows:
  • the sterile catheter combination electrode is placed in a venous blood vessel of the patient and the elec ⁇ trode lead connected to the patient channel of the analyzer;
  • stat combination electrode is placed in a standard solution (which need not be sterile) of 4.0 milli- equivalents K/L and the electrode lead is connected to the stat channel of the analyzer;
  • the patient channel is adjusted to read the same value as the stat channel. For example, if the fresh blood sample reads 2.5 on the stat channel using the stat electrode, adjust the patient channel to read 2.57. To recheck the calibration the indwelling catheter electrode, simply repeat steps 4), 5) and 6) . This simple and reliable calibration method takes no more time than a few seconds.
  • the ion selective and reference electrodes are inserted together, as separate units or as a combination electrode, into the patient's blood. They may be inserted into the flow through a by-pas or directly into a vein. Those electrodes are connected to the measuring channel of the dual channel analyzer. Anothe selective electrode and reference electrode pair are con ⁇ nected to the calibration channel of the instrument and are inserted in a standard potassium solution. The reference channel Is adjusted until the reference display indicates the potassium content of the standard solution. A sample o the patient's blood is drawn. The ion sensitive electrode and the reference electrode of the calibration pair are moved from the standard solution to the blood sample. The display indication is noted and the measuring channel is then adjusted to provide that same indication. If the physician has any doubt about the accuracy of the reading on the measurement display, he need only draw a blood sam- pie and measure it with the calibration electrodes. Agree ⁇ ment of the measurement and calibration display indications is evidence that the measurement is accurate.
  • the potassium measurements are continuous and current, and the cost of making the measure ⁇ ments is generally much less than the cost of a half dozen or more laboratory tests of blood samples.
  • Two channel analyzers need not be expensive. They can be small, light ⁇ weight, and easily portable. It is entirely feasible to move the analyzer and the electrodes with the patient from operating room to the intensive care unit or elsewhere.
  • the method provides another very special benefit.
  • the two electrode sets are subjected to the same sample material.
  • the fluids of the body have the same effective ⁇ ness as an electrolyte everywhere in the body. Any varia ⁇ tion will be so minor as to make no practical difference.
  • the reference electrode used for measurement and cali ⁇ bration will be subjected to the same electrolyte, there is no need to provide a standard KC1 or other electrolyte.
  • the method of the invention is employed, the conven ⁇ tional salt bridge and the electrolyte body can be eliminated.
  • the two reference electrodes become no more than a silver wire with a small amount of silver chloride bonded to the wire at the end or other point that will be immersed in the blood or other body fluid.
  • the silver wire may be very thin, indeed, and th silver chloride no more than a spec at the end of the wire Not only has the physical size been reduced, but so has th cost.
  • a combination electrode can be considered to be disposable and it is a feature of the invention to provide an improved reference electrode and an improved combinatio electrode for use in the method.
  • the materials employed in the reference half cel are the same, in the preferred embodiment, as are used in the "half cell" portion of the ion selective electrode. If silver, silver chloride, silver black, and platinum black are included in one, they should be included in the other.
  • the electrodes are package in a controlled environment. They are packaged with their active, electrode surfaces in a reference or calibration solution. The remainder, except for electrical leads to be used for calibration in the package, is contained in a sealed, sterile package.
  • Figure 1 is a cross-sectional, schematic showing of part of a prior art ion selective elec ⁇ trode
  • FIG. 2 is a cross-sectional, schematic view of another electrode which incorporates some features of this invention.
  • Figure 3 is a greatly enlarged cross- sectional, schematic view of still another sensor structure which incorporates additional features of the invention.
  • Figure 4 is a cross-sectional view illus ⁇ trating how the sensor of Figure 3 is mounted to produce a needle-like structure
  • Figure 5 is an elevational view of an electrode which embodies the sensor of Figures 3 and 4 and is useful for in vivo monitoring of potassium in blood;
  • Figure 6 is an elevational view of a sen- sor which embodies the invention and is made for industrial applications;
  • Figure 7 is a cross-sectional view of a reference electrode for use in the invention
  • Figure 8 is a cross-sectional view of a combination electrode which combines the electrode structures of Figures 4 and 7;
  • Figure 9 is a cross-sectional view taken on line 9-9 of Figure 8.
  • Figure 10 is a diagram illustrating how th sensor sets and the analyzer are arranged in prac ⁇ ticing the method of the invention
  • Figure 11 is a view in fron elevation, and partly in section, of a pair of sensor disposed in a reference solution and in a sterile package;
  • Figure 12 is a view in front elevation, and partly in section, of a combination electrode in catheter form disposed in a reference solution and a sterile package.
  • the invention is applicable to ion selective electrodes other than potassium electrodes, and it is applicable to sensors in a wide range of physical sizes and shapes.
  • the invention solves what has been a difficult and limiting problem in that it makes possible in vivo sensing of potassium using the best potassium selective materials that are currently available. In vivo sensing of potassium is the best known mode for practicing the invention and that mode has been selected for detailed description here.
  • the best potassium ion selective membrane cur ⁇ rently available appears to be the membrane described by D. M. Bank, J. Kratochvil and T. Treasure in the Journal of Physics, volume 265, published in 1977 at pages 5 and 6.
  • the membrane is formed by dissolving the following list of ingredients in 3 ml of tetrahydrofuran and then evaporating the solvent material.
  • the product of that process is a PVC membrane essentially hydrophobic, whose hardness or flexibility is a function of the density and quantity of the constituent PVC and the plasticizer.
  • the material is sometimes referred to herein as PVC or potassium selec- tive PVC.
  • this PVC material is formed into a thin membrane, cut discs of which are glued to the end of a PVC tube.
  • the interior of the tube is filled with an electrolyte.
  • the electrolyte is usually a solution con ⁇ taining KC1.
  • a half cell is immersed in the electrolyte.
  • the half cell may be formed by dipping a silver wire in molten silver chloride.
  • An electrode thus described is shown in Figure 1 of the drawing.
  • the ion selective PVC membrane 10 is secured to the end of tube 12 by a polymer adhesive shown as a thin annulus 14 at the end of the PVC tube.
  • a plug 16 inside the tube at a point removed fro the membrane serves to retain the body 18 of electrolyte i contact with the membrane 10.
  • a chlorided silver wire 20 extends through the plug into the electrolyte to form a ha cell 22.
  • the electrolyte is a solution of potassium chlor
  • Such an electrode in this and other physical forms, has proven to be a stable measuring instrument. Such electrod are commercially available in tubular form. Typical diame are 5 mm to 12 mm. Typical life Is one to six weeks. The membrane 10 can be replaced when exhausted. Theri cost varies from almost one hundred to several hundred dollars s they can not be called ''disposable" and they have not been cost effective. Attempts at miniaturization to diameters o 1 to 2 mm have been less than successful, primarily because of difficulty in controlling the distribution of adhesive when attaching miniature membranes to the shank tube.
  • this electrode can be improve by the inclusion in the half cell structure of one or both of the materials silver black and platinum black. Only small quantities are required. Their inclusion increases
  • Silver black and platinum black are comparable in effect when used alone, but the effect is enhanced when they are applied together. They can be used as sub ⁇ stitutes for silver chloride although not identical to silver chloride in operation: Silver chloride has low d.c. polarization for measurement of d.c. current, but has high A.C. polarization. Platinum black exhibits the opposite effect.
  • These materials have the very great advantage that they can be incorporated in the metal-metal salt paste mixture that is sintered on the conductor wire to form the half cell, or they can be applied as coatings over the sur ⁇ face of the half cell and over one another. They are simply applied by dipping the half cell in a suspension of silver black in a carrier that is evaporated away. Similarly, the platinum black may be applied by dipping the half cell and its silver black coating in a suspension of platinum black. The carrier is then evaporated away to leave a platinum black overlayer.
  • the half cell of Figure 2 was made by that process. It comprises a silver wire 32 whose end has been coated with a paste of silver and silver chloride particles. The paste was driven off and the silver and silver chloride par- tides were bonded to one another and to the wire by sintering.
  • the half cell was dipped into a suspension of silver black and platinum black in tetrahydrofuran and a plasticizer. It was withdrawn and allowed to dry. In this case, the plas ⁇ ticizer was ethylene glycol. On removal, the half cell was dried to leave a layer of silver black and platinum black containing a small quantity of ethylene glycol.
  • the half cell so prepared is designated 34 in Figure 2. It is drawn into the end of a protective tube 36 of PVC such that part of it protrudes. Thereafter, it is dipped into a potassium ion selective PVC membrane of kind that is described above. It is dipped once or twice into that solution such that the protruding end of the ha cell is covered and such that the end of the PVC tube is sealed. The PVC coating is dried to produce the elec ⁇ trode shown in Figure 2.
  • the unit of Figure 2 can be made in 2 to 3 mm diameter size, but its performance is not as good as the unit shown in Figure 1 because it tends to drift. None ⁇ theless, it is very much better than a unit which omits the silver black and the platinum black, notwithstanding that those materials are formed in coatings over the basic half cell material rather than being mixed with them.
  • the electrode of Figure 2 can be made to work as well and even better than the electrode of Figure 1 by the addition of another layer of material.
  • a layer of immo ⁇ bilized electrolyte is added between the half cell materia and the outer, ion selective layer. That can be accom ⁇ plished by adding a layer of hydrophilic or porous organic material over the half cell and then sealing that layer in place with the outer ion selective layer.
  • Water can be added to this water absorbent layer (hereafter referred to as a hydrophilic layer) either before or after addition of the outer layer. If not included as part of the materi of the electrolyte layer, water can be introduced through the outer layer as in the case of the electrode of Figure 2. Electrodes which incorporate such an hydrophilic layer are shown in Figures 3 and 4.
  • the hydrophilic layer is visible in Figure 3 where it is designated 40.
  • the outer layer 42 is formed of potassium selective PVC as described above.
  • the layer 44 below the hydrophilic layer is platinum black.
  • Layer 48 is sintered silver and silver chloride bonded to a silver wire 50. This unit was constructed by forming the initial silver-silver chloride half cell and successively dipping it into a suspension of silver black and platinum black, hydrophilic gel material and the potassium selective PVC membrane solution.
  • Layer 40 was formed from a solution prepared as follows:
  • the half cell was dipped in that mixture to cover under layers of half cell material and allowed to dry while the conductor wire was suspended end down.
  • the dashed line that separates the electrolytic layer 40 from the potassium selective layer 42 represents that there is no clear line of demarkation between the two as a consequence of the plasticizing action of the plasticizer.
  • the bulbous sensor 60 When the bulbous sensor 60 has been produced and is dried, it may be mounted at the end of a supporting struc ⁇ ture that facilitates the proposed application.
  • the sensor bulb In Figure 4, the sensor bulb is shown to be fastened by an urethane adhesive material 62 into the end of a 2 millimeter outside diameter polyvinyl chloride tube 64 to form a needle shaped electrode thin enough to be inserted into a patient's blood ⁇ stream.
  • the whole of the unit is depicted in Figure 5 where the tube 64 extends into a handle portion 66 from which a shielded conductor 68 extends.
  • FIG. 6 That the invention is applicable to other physi cal arrangements is depicted in Figure 6 where it is hous in a package suitable for industrial application. Howeve it is the in vivo, potassium level application that is mo interesting.
  • the needle shaped electrode of Figures 3, 4 and 5 can be mass manufactured and produced at a small fraction of the cost of the electrode, of Figure 1. It ca be inserted into a patient and used to- monitor potassium level during an operative procedure. It will maintain it calibration and the sensor may simply be left in place while the patient is moved from the operating room to a critical care unit or intensive care room. When no longe needed by the patient, it is disposed.
  • An important element in the electrolyte layer i the hydrophilic or porous organic material. It may have variety of forms. The requirement is that it accept and retain an electrolyte. In preferred form, it should be reduceable to a liquid or semi-liquid that permits its being coated on a half cell in a dipping or spraying pro ⁇ cess and then dried sufficiently to permit subsequent add tion of an overlayer of ion selective membrane material preferably by dipping or spraying.
  • the electrolyte layer It is advantageous to have water contained in the electrolyte layer so that prolonged soaking is not required prior to use. On the other hand, it matters not whether the water is included in the hydrophilic layer when applied or is added later.
  • the hydrophilic material might be a readily wetted expanded plastic which is dry after being applied over the half cell material. Water could be added to such a material just prior to addition of the ion selective over-material. It now appears, however, that the form most likely to per ⁇ mit close control of quality, and that is least expensive, to produce, is to form the electrolyte layer as a gel.
  • a wide variety of suitable gels is available. Animal gels are satisfactory. A variety of resins are commercially available in gel form and are likely to be more uniform.
  • the reference electrode for use in the method of the invention comprises a metal wire 70 on the active end 77 of which is a coating 72 of the salt of that metal.
  • a preferred form employs a silver wire as the wire 70.
  • the inner coating 72 is silver chloride with an overlayer 74 of silver black and platinum black, and an outer layer of protein material 76.
  • the reference electrode is equivalent to the silver wire 50 and silver chloride covering 48, and the silver black and platinum black coatings 44 and 46 of Figure 3.
  • the material of the refer- ence electrode half cell and the ion selective half cell are the same. In most cases both will have silver chloride bonded to a silver wire. If one has a coating of silver blakc, so should the other. If one includes platinum black, so should the other.
  • the reference electrode is "pre-poisoned" by being coated with a very thin layer of protein. That can be accomplished by soaking the otherwise completed reference cell in animal gelatin for an hour or two.
  • a flexible triple tube 80 is formed with three openings which extend in parallel over the length of the tubing. One end is fastened to an end fitting 82 and the other end is cut off on the bias as best shown in Figure 8. The three openings are numbered 83, 84 and 85 for identi- fication.
  • the sensor of Figure 3 is shown disposed in opening 83. Its multilayered sensing end 60 is exposed at the cut end of the tubing 80. The silver wire 50 ex- tends through the opening 83 back to the connector 82.
  • a plug 86 of epoxy fixes the selective sensor 60 in place and seals the opening.
  • Another plug 88 of epoxy fixes the reference electrode in place in opening 84 with the silver chloride body exposed at the cut end of the tube.
  • the other opening 85 serves as the catheter opening.
  • the reference electrode and the ion selective sensing electrode are connected to the shield braid and the center conductor, respectively, of a coaxial cable at the connector 82.
  • th two electrodes permit measurement of the potential across the ion selective membrane of the sensing electrode at the analyzer to which the coaxial cable is connected.
  • a two-channel analyzer is depicted In Figure 10.
  • the instrument shown is arranged to measure potassium level in an unknown sample or in a known standard solution. It matters not whether the analyzer is formed by two separate single channel instruments or is a single instrument which operates on a time share basis to provide two separate chan nels. What is important, is that the two channels provide substantially accurate and corresponding indications when used to measure the same sample.
  • the display 102, the input terminal 104, and the calibration or scale control 106 are part of the channel that is to be used to measure unknown samples.
  • the display 102 is labelled "PATIENT.”
  • the other channel has a display 108 marked “STAT,” a cali ⁇ bration or scale control 110 and a coaxial cable input 112.
  • the standard solu ⁇ tion tube 114 contains a body 120 of 4.0 m Eq. K/L solution as indicated by the numerals in the display 108.
  • the cali ⁇ bration knob 110 was rotated until those numerals appeared in the display 104.
  • the other sample tube 122 contains a quantity of blood.124. If the combination electrode catheter 79 is moved from tube 114 and is inserted in the blood in tube 122, and if the calibration knob 110 is not moved, the display 108 will change to display the level of potassium in the blood sample 124. In this example, let it be assumed that the numerals 3.85 appeared in display 108 when measuring the potassium level in sample 124.
  • ion selective and reference electrodes are to be used to measure potassium level in the blood of a patient being dialyzed.
  • the flow cell 130 is assumed to be connected in series in the bypass by which the patient's blood is delivered to and returned from the dialysis machine.
  • the potassium ion selective electrode 132 and the reference electrode 134 are mounted at closely adjacent points of the cell. Both electrodes are arranged to extend into
  • the ion selective electrode 132 is like the electrode of Figure 3 and the reference electrode is like the electrode of Figure 7. Thus, they are like the corresponding elec ⁇ trodes in catheter unit 78.
  • the two electrodes 132 and 134 are connected to the center conductor and shield braid, respectively, of a coaxial cable 136 which is connected to the sample channel input 104. Since the blood measured by electrodes 132 and 134 in the cell is the same as the blood sample 124, it, too, must have 3.85 millileters equivalent potassium per liter if the sample 124 was drawn shortly before and if there was no intervening event which could have changed the potassium level. All that remains is to turn the cali bration knob 106 until the numerals in the "PATIENT" , dis ⁇ play 102 are 3.85. Thereafter, the display 102 will chang only if the potassium level In the blood has changed. The catheter 78 is left in the standard solution 120.
  • the "ST display 104 will continue to display 4.0. If the surgeon or the intensive care nurse wants to verify that the dis ⁇ played value of potassium level is correct, a blood sample 124 is drawn and placed in a clean container 122, and the electrode assembly 78 is transferred from the reference solution 120 in tube 114 to the blood sample in tube 122. The reading at display 108 should be the same as that appe ing at the patient display 102. If there is a difference in the readings, it is patient display 102 which is then adjusted. The indwelling electrode is now calibrated with out having removed it from, and replacing it back into, the patient.
  • a reference electrode 144 and an ion selective electrode 146 are mounted in openings * along the length of the cell.
  • Plastic disposable caps 148 and 150 seal the ends of the cell which is filled with a body 152 of reference or calibration solution.
  • the conductor terminals 154 and 156 extend out of the package 140 and are bonded by a pressure adhesive to the upper margin of the package to preserve the sterility of the interior. By this means the electrodes are pre-soaked. They can be converted to the analyzer and the latter calibrated without opening the package.
  • the package is torn open to provide access to the cell.
  • the end caps are removed and the cell is inserted in a flow line. There ⁇ after, the package is removed entirely or, in certain environ ⁇ ments in which it is desirable not to expose any adhesive, all but the portion 160 around the electrodes is removed.
  • Figure 12 shows a similar arrangement except that the two electrodes are mounted together as a combination electrode 162 in a flexible catheter.
  • the active portions are disposed in a vial 164 filled with a reference liquid 166.
  • the stopper of the vial is slid along the catheter tube back to the connector block 168 when the sterile pack ⁇ age 170 is opened.
  • separate temporary connec ⁇ tors 172 and 174 are attached to the terminals of block 168.
  • Lead wires 176 and 178 extend from the package to permit calibration before the package is opened. In this case, the package is not evacuated.

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Abstract

Une electrode de selection d'ions pouvant etre produite sous forme miniaturisee, convenant au controle in vivo est obtenue en recouvrant une demi cellule (48) de sel de metal-metal avec une couche (40) d'un materiau hydrophile contenant un electrolyte avec une couche superieure (42) constituee par une membrane de selection d'ions. Les couches peuvent etre appliquees par un procede d'immersion et de sechage. La stabilite est augmentee grace a l'adjonction de noir d'argent (46) et de noir de platine (44) a la demi cellule, ces materiaux pouvant etre ajoutes en tant que couches lors d'un procede similaire d'immersion et de sechage. Une demi cellule d'electrode de reference complementaire est fabriquee avec le meme materiau utilise pour la fabrication de la partie "demi cellule" de l'electrode de selection, avec la seule exception que la demi cellule de reference est recouverte d'une couche de proteine. Un emballage special et un processus special facilitent l'etalonnage.
PCT/US1981/000049 1980-01-28 1981-01-12 Electrodes de selection d'ions et procede d'etalonnage de celles-ci WO1981002218A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
DE8181900665T DE3171358D1 (en) 1980-01-28 1981-01-12 Ion selective electrode
AT81900665T ATE14352T1 (de) 1980-01-28 1981-01-12 Ionenselektive elektrode.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US06/116,297 US4340457A (en) 1980-01-28 1980-01-28 Ion selective electrodes
US116297 1980-01-28

Publications (1)

Publication Number Publication Date
WO1981002218A1 true WO1981002218A1 (fr) 1981-08-06

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PCT/US1981/000049 WO1981002218A1 (fr) 1980-01-28 1981-01-12 Electrodes de selection d'ions et procede d'etalonnage de celles-ci

Country Status (6)

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US (1) US4340457A (fr)
EP (1) EP0044869B1 (fr)
JP (1) JPS6356498B2 (fr)
AU (1) AU549380B2 (fr)
CA (1) CA1169491A (fr)
WO (1) WO1981002218A1 (fr)

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EP0155638A2 (fr) * 1984-03-15 1985-09-25 EASTMAN KODAK COMPANY (a New Jersey corporation) Electrode sensible aux ions potassium
EP0193676A1 (fr) * 1985-02-07 1986-09-10 Spectramed, Inc. Electrode à l'état solide
EP0270751A2 (fr) * 1986-12-11 1988-06-15 Horiba, Ltd. Solution d'électrolyte pour usage dans des électrodes pour la mesure d'ions et son procédé de fabrication
EP0289199A1 (fr) * 1987-04-28 1988-11-02 Ie Sensors, Inc. Cathéter
US4892640A (en) * 1985-04-16 1990-01-09 Avl Ag Sensor for the determination of electrolyte concentrations
EP0352708A2 (fr) * 1988-07-25 1990-01-31 Abbott Laboratories Emballage pour un dispositif médical stérilisable calibrable
DE19536315A1 (de) * 1995-09-29 1997-04-03 Knick Elektronische Mesgeraete Verfahren und Vorrichtung zur Überwachung von automatisierten pH-Messungen
WO1998037800A1 (fr) * 1997-02-27 1998-09-03 Minnesota Mining And Manufacturing Company Cassette pour etalonnage tonometrique
US5958782A (en) * 1993-10-21 1999-09-28 Minnesota Mining And Manufacturing Company Cation-sensing composite structure and compounds for use therein

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Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0074498A1 (fr) * 1981-09-04 1983-03-23 F. HOFFMANN-LA ROCHE & CO. Aktiengesellschaft Procédé et dispositif d'étalonnage de capteurs
EP0155638A2 (fr) * 1984-03-15 1985-09-25 EASTMAN KODAK COMPANY (a New Jersey corporation) Electrode sensible aux ions potassium
EP0155638A3 (en) * 1984-03-15 1987-06-24 Eastman Kodak Company Potassium-ion-selective electrode
EP0193676A1 (fr) * 1985-02-07 1986-09-10 Spectramed, Inc. Electrode à l'état solide
US4892640A (en) * 1985-04-16 1990-01-09 Avl Ag Sensor for the determination of electrolyte concentrations
EP0270751A3 (fr) * 1986-12-11 1989-10-04 Horiba, Ltd. Solution d'électrolyte pour usage dans des électrodes pour la mesure d'ions et son procédé de fabrication
EP0270751A2 (fr) * 1986-12-11 1988-06-15 Horiba, Ltd. Solution d'électrolyte pour usage dans des électrodes pour la mesure d'ions et son procédé de fabrication
EP0289199A1 (fr) * 1987-04-28 1988-11-02 Ie Sensors, Inc. Cathéter
EP0352708A2 (fr) * 1988-07-25 1990-01-31 Abbott Laboratories Emballage pour un dispositif médical stérilisable calibrable
EP0352708A3 (en) * 1988-07-25 1990-10-10 Abbott Laboratories Packaging for a sterilizable calibratable medical device
US5958782A (en) * 1993-10-21 1999-09-28 Minnesota Mining And Manufacturing Company Cation-sensing composite structure and compounds for use therein
DE19536315A1 (de) * 1995-09-29 1997-04-03 Knick Elektronische Mesgeraete Verfahren und Vorrichtung zur Überwachung von automatisierten pH-Messungen
DE19536315C2 (de) * 1995-09-29 1998-01-15 Knick Elektronische Mesgeraete Verfahren und Vorrichtung zur Überwachung von automatisierten pH-Messungen
WO1998037800A1 (fr) * 1997-02-27 1998-09-03 Minnesota Mining And Manufacturing Company Cassette pour etalonnage tonometrique
US5997818A (en) * 1997-02-27 1999-12-07 Minnesota Mining And Manufacturing Company Cassette for tonometric calibration

Also Published As

Publication number Publication date
JPS57500171A (fr) 1982-01-28
EP0044869A4 (fr) 1982-12-20
CA1169491A (fr) 1984-06-19
AU549380B2 (en) 1986-01-23
JPS6356498B2 (fr) 1988-11-08
AU6920181A (en) 1981-08-17
EP0044869A1 (fr) 1982-02-03
EP0044869B1 (fr) 1985-07-17
US4340457A (en) 1982-07-20

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