TRANSCUTANEOUS CARBON DIOXIDE MEASURING ASSEMBLY

Abstract: A transcutaneous carbon dioxide measuring assembly integrally composed of three components, the first compo­ nent comprising a top cover 24 centrally locating a glass electrode having an H⁺ ion sensitive glass membrane 17 at the end of a tubular member 18 made of an insulating material, a conductive coating 19 formed on the inner surface of the glass membrane 17, an external reference electrode 23 located around the glass electrode and lead wires 14 are connected to the conductive coating 19 and the external reference elec­ trode 23, the second component comprising a heater member 28 which has a heater and a heat sensitive element and the third component comprising a membrane holder 25 having a polymer membrane 25 which is CO₂ permeable stretched between the ends thereof, the third component being dis­ posed between the first component and the second compo­ nent.

Description: TRANSCUTANEOUS CARBON DIOXIDE MEASURING ASSEMBLY The present invention relates to a CO2 measuring assembly suitable for the transcutaneous measurement of the concentration of carbon dioxide (or of the partial pressure thereof) in the tissue metabolism or in the blood. Detecting the concentration of CO2 in the blood is extremely important for clinical tests for studying breathing and metabolism and for determining the approximate pH value of the blood of the patients. A method of direct measurement by withdrawal of the blood from an artery for detecting the CO2 concentration in the blood is known. This method was, however, not suitable for continuous measurement and caused pain to the patient. This method was particularly not suitable for the neonatal and premature babies because of the possible risks when collecting blood from the patients. A transcutaneous measuring electrode assembly is also known wherein carbon dioxide which diffuses from the blood or tissue is trapped at the skin surface and chronological continuous measurement without causing pain to the patient is made possible. The present invention relates to an improvement in the transcutaneous measurement of carbon dioxide in the blood, and, more particularly, to the improvement made to the structure of the glass electrode, to the heating structure and to the signal to noise ratio of the input signal. According to the present invention there is provided a transcutaneous carbon dioxide measuring assembly integrally composed of three components, the first component comprising a top cover 24 centrally locating a glass electrode having an H+ ion sensitive glass membrane 17 and the end of a tubular member 18 made of an insulating material, a conductive coating 19 formed on the inner surface of the glass membrane 17 an external reference electrode 23 located around the glass electrode and lead wires 14 are connected to the conductive coating 19 and the external reference electrode 23, the second component comprising a heater member 28 which has a heater and a heat sensitive element and the third component comprising a membrane holder 25 having a polymer membrane 25 which is C02 permeable stretched between the ends thereof, the third component being disposed between the first component and the second component. The conductive coating is preferably a metal or metallic salt which may be formed by vacuum deposition on the inner surface of an H+ ion responsive glass membrane comprising a glass electrode, a lead wire for the glass electrode being connected to the metal or metallic salt coating layer, and the glass membrane also being reinforced by a resin such as silicone rubber inside the glass container forming the glass electrode The carbon dioxide measuring electrode of the assembly of the present invention does not require such electrolyte filled in the glass container of the prior art assembly, and is free from all the problems and difficulties mentioned above. Accordingly, the present invention provides a transcutaneous carbon dioxide measuring assembly which is stable, robust and efficient to operate. In the assembly of the present invention, the skin heating part is divided into two parts, namely the heating member which has a heater 10 and a heat sensitive member 11, and the skin heating end portion which has a skin heating surface screwed to the heater member. Thus, the lead wire to the electrode, the lead wire to the heat sensitive member and the feed wire to the heater may be housed within a single cord, thus the C02 measurement assembly of the present invention offers an excellent workability. According to the present invention, there is further provided a structure wherein the glass electrode itself is heated by the heating member under suitable temperature control. This temperature stabilized glass electrode limits the heating area to the proximity of the measuring portion and reduces the skin area which is to be heated, thereby eliminating further the possibility of neonatals suffering from burns. In the conventional assembly, the input impedance to the preamplifier has to be raised because of an extremely high impedance between the electrodes, and the preamplifier of the measurement device provided at a distance from the electrode assembly sensor magnetic induction suffers from electro-static and elecrtro-magnetic induction. However, according to the present invention, the preamplifier contained in the glass electrode is connected to the measurement device with a low output impedance of the preamplifier. Thus, the difficulties concerning the noise caused by the high input impedance of the preamplifiers are removed. Since the preamplifier is contained in the thermostat glass electrode, fluctuations in the preamplifier gains and drifts in the offset based on the temperature changes are extremely small. The present invention will be further described with reference to the accompanying drawings, in which: Figure 1 is a cross sectional view of a conventional carbon dioxide measuring electrode assembly; Figures 2(a) and 2(d) are cross sectional views of a carbon dioxide measuring assembly in accordance with a first embodiment of the invention; Figure 3 is a cross sectional.-view of a carbon dioxide measuring assembly in accordance with a second embodiment of the invention; Figure 4 is a cross sectional view of a carbon dioxide measuring assembly in accordance with a third embodiment of the invention; Figure 5 is a cross sectional view of a carbon dioxide measuring assembly in accordance with a fourth embodiment of the invention; and Figure 6 is a schematic diagram of the circuit for the preamplifier of Figure 5. Figure 1 is a cross sectional view showing the basic structure of a conventional type carbon dioxide measuring electrode assembly. The assembly shown in Figure 1 comprises three separate members which are a top cover 7 centrally locating a glass electrode 5 comprising a glass container 2 having an H+ ion sensitive (pH responsive) glass membrane 1 at the bottom thereof and containing a buffer electrolyte 3 mainly composed of an aqueous solution of KC1 or NaCl and a silver wire 4 immersed therein the surface of which has been converted into silver chloride, and having an external reference electrode 6 made of silver and silver chloride located around the glass electrode 5, a membrane holder 9 stretching an electrode membrane 8 at the end portion of the holder 9, and a heating member 12 having a heater means 10 embedded therearound and a heat sensitive element 11 embedded therein. The membrane holder 9 being detachably retained between the top cover 7 and the heating member 12 the screws 16. Between the electrode membrane 8 and the glass membrane 1 are the electrolyte 13 comprising an aqueous solution of NaHC03, NaCl or KC1, and a spacer made of paper or nylon, etc. The reference number 14 denotes a lead wire from the electrodes,15a a lead wire from the heat sensitive element 11, and 15b a feed wire to the heater 10. The electrode assembly having an electrolyte contained in the glass electrode as mentioned above has the following defects: i) When the assembly is knocked over or is inverted by the movement of a patient, the electrolyte 3 touched accidentaly moves away from the glass membrane 1 and silver wire 4 is thus electrically disconnected from the glass membrane 1; ii) The electrolyte is accidentally frozen during preservation or transportation in a very cold climate and this causes the glass electrode to break; iii) When the temperature of the electrode 5 assembly is elevated during measurement, a portion of the electrolyte 3 vaporizes and forms dew in the glass container 2 and causes abnormalities in the measurement; iv) The electrolyte of the glass electrode 5 accidentally leaks and causes the insulation of the electrode to deteriorate; v) The glass membrane is susceptible to being broken; vi) The temperature of the glass electrode affects its electro motive force so that it is necessary to maintain the temperature fluctation of the electrode within +0.2 0C. However, it is difficult to maintain the temperature of the electrode so stable; vii) The conventional type electrode assembly has two separate components of a top cover 7 having a glass electrode and an external reference electrode therearound, and a heating member 12 having a heater 10 and a heat sensitive element 11. Therefore, it is necessary for lead wires 14, lead wires 15a and feed wire 15b to be connected to the top cover and the heating member 12 respectively. Because of the construction having these separated lead wires, it is not possible to fix the heating member 12 and the top cover 7 by way of a screw means, but the bolts 16 must be used instead. As three bolts do not uniformly tighten the top cover and the heater fixed to each other at the times when the membrane holder is changed, the measured values fluctuated. Since the outer diameter of the electrode assembly is as small as 18 mm, a tiny screw of 1 mm ¯ must be used. Thus, the replacement of the membrane holder is extremely difficult; and viii) In conventional electrode assemblies, however, a pH responsive glass membrane placed on the bottom of the glass electrode shows an extremely high impedance such as 109 ohm to 1010 ohm, so that the lead wires 14 tend to take up noises causes by electro static and/or electro-magnetic induction. In Figures 2(a) to 2(d) there are shown cross section of the transcutaneous carbon dioxing measurement assembly according to a first embodiment of the present invention as well as those of the three main components of the measurement assembly. An H+ ion sensitive glass membrane 17 is attached to an insulated glass tube 18 by fusing or with an adhesive to form a glass container. A conductive coating 19 of a thin film of Ag, Pt, or Au, is formed over the inner surface of the glass membrane 17 and on a part or the whole surface of the glass tube 18 by vacuum deposition, or by other electroless plating or ion plating techniques. The lead wire 20 for the glass electrode is connected to conductive coating 19 by soldering or with a conductive adhesive 21. A hardening type liquid rubber or heat hardening resin, such as silicone rubber or an epoxy resin is filled inside the glass electrode to reinforce the lead wire fixing point and the glass membrane 17. An external reference electrode 23 made of silver/silver chloride is provided over the outer circumference of the glass electrode. The glass electrode and the external reference electrode 23 are fixed to the top cover 24 made from a synthetic insulating resin. A hollow cylindrical membrane holder 25 made from a synthetic resin such as polyethylene has attached thereto a polymer membrane 26 of a C02 permeable and yet hydrophobic film. The polymer membrane 26 is pressed onto the glass membrane 17 under tension caused by squeezing a thin film of an electrolyte 27 comprising an aqueous admixture of NaHC03, NaCl or KC1 between the membrane and the end of the heating member 28. 14 denotes lead wires from the electrodes, 15a lead wires from a heat sensitive sensor and 15b feed wires to the heater, respectively. Figures 2(b).(c) and (d) respectively show the three components of the assembly as shown in Figures 2(a), namely the top cover 24, the membrane holder 25 and the heater member 28. A specific example of a sensor according to Figures 2(a) to 2(d)is described below. An H+ ion sensitive glass membrane 17 having a composition of Na20 25 wt%, CaO 6 wt%, and SiO2 72 wt% is fused onto an insulating lead glass tube 18. The glass container was dried for 2 hours at 200 C, and the internal bottom surface thereof was spattered with o silver at 600 A by ion spattering, and 50 Iwm, of silver was further vacuum deposited thereon. To connect the lead wire 20 with the conductive coating 19, a silver-containing epoxy resin 21 was used. The portion denoted by the number 22 in Figures G(a) and 2(b) was filled with, silicone rubber which hardens at normal temperatures (KE67RTV made by Shinetsu Kagaku). The external reference electrode 23 made of silver/silver chloride shown in Figure 2 was assembled using identical materials an an identical method to those of the prior art. The properties of the sensor according to the present invention and those of the conventional sensor are given in Table 1 for comparison. In the experiment identified in Table 1, an aqueous solution containing 0.005 mol NaHCO3 and 0.02 mol NaCI as electrolyte 13, 24, and saturated with AgCl was used and a 25/us thick film of poly-tetra fluoroethylene was used for both polymer membranes 8, 26. The electrodes were both heated and maintained at 43.50C. The other conditions are given in Table 1, the same conditions be employed for the conventional sensor and the sensor of the present invention. Table 1 Performance of the Conventional Sensor and the sensor of the present invention Conventional Present Inven Type ion Response time (gas) (90%) 35 sec 35 sec (CO2 5% - 10%) Sensitivity (gas) Potential Potential difference difference (CO2 5% --10%) 16 mV 16 mV Measurement 1. Neonatal 30 31 taken on (3 days old) humans: 2. Infant Too active & 35 measurement impossible (3 years old) 3. Adult 41 39 (healthy subject) 4. Adult 45 45 (pulmonary oedema patient) As is showniin Table 1, the sensor according to the present invention not only performed not significantly differently from the prior art sensor, but also has the characteristics discussed above. The sensor of the present invention is superior to the prior art sensor as a transcutaneous carbon dioxide measurement assembly. In this example the conductive membrane for reading the potential was a deposited membrane, and it is possible to form the conductive coating 19 by means of wet electroless plating using the silver mirror reaction. It is also possible to form a conductive coating (19) by applying, for instance, a conductive adhesive agent such as Do-tite D-723S. Using a sensor of the present invention, it is possible to measure H+ ion concentration changes (pH changes) without using an electrolyte inside the glass electrode so that: a) it is possible to continue the measurement without impairing the function of the sensor when it becomes inverted or falls due to the movement of the patient, b) it is possible to avoid problems such as damage to the glass electrode as the electrolyte inside the container becomes frozen in cold climates, c) there is no abnormal behaviour of the potential due to vaporization and dew concentration of the electrolyte in the hollow portion of the glass electrode when the sensor is heated, d) there are no difficulties caused by the leakage of electrolyte from the glass electrode, e) the mechanical strength of the H+ ion sensitive glass membrane increases since a solid body such as a metal or silicone or epoxy resin is filled inside the glass electrode, thus making the sensor less liable to breakage. Figure 3 shows a cross sectional view of a second embodiment of the transcutaneous carbon dioxide measuring assembly of the present invention. Referring to Figure 3, an H+ ion responsive glass membrane 30 is fixed to the end of an insulated glass tube 31, by fusing or with an adhesive agent to form the glass container. As alternatives the glass tube 31 may be made of ceramic or a plastics material. A conductive coating 32 of a metal such as Ag, Pt, Au, or of a metallic salt such as AgCl or AgI is formed over the surface of the glass membrane 30 and over a part of the whole surface of the glass tube 31 by vacuum deposition, ion plating, etc. The metallic salt which has a lower melting point that the glass may be thermally fused onto the glass surface to form a conductive film. Head wire 33 for the glass electrode is connected to the film of the metal or the metallic salt by fusing or with a conductive adhesive agent. A hardening type liquid rubber or heat hardening resin 34 such as silicone rubber or an epoxy resin, is filled in the glass electrode to reinforce the fixing portion of the lead wire and the glass membrane. An external reference electrode 35 made of silver/silver chloride is provided outside the glass electrode. The assembly also comprises an electrode main body 38, integrally provided with a heater member 36 comprising a heater 42 and a heat sensitive element 37, a membrane {^ holder 41 which holds a polymer membrane 39 at the ends thereof, the membrane being made of a carbon dioxide permeable but hydrophobic film, and a heater end portion 40, which causes the polymer membrane 39 to be pressed onto the glass membrane 30 of the membrane holder 41 under tension by squeezing a thin electrolyte film of a mixed aqeuous solution of NaHCl37NaCl, or KC1, and screwing screw 43 of the heater member 36 ¯f the electrode body 38. The electrode main body, the membrane holder and the heater ehd portion are independent of each other and may be assembled into one unitary body. The heater end portion 40 heats the measuring portion by transmitting heat to the patient's skin. A multicore cord 29 houses the lead wires to the electrodes, the lead wires to the heat sensitive member and the feed wires tut the heater. A specific example of the transcutaneous carbon dioxide measuring assembly shown in Figure 3 is described below. The glass membrane 30 consisting of 25% of Na20, 10 wt/% of CaO, and 65 wt% of SiO2 having a thickness of 0.15 mm was fused to the end of a lead glass cylinder by soldering. Platinum was vacuum deposited inside the glass container and the lead wire was attached thereto using a low fusing point solder. Silicone rubber of a type which hardens at normal temperatures was then poured into the glass container and hardened. Over the outer circumference of the glass electrode a silver ring having a surface which had been electrolysed to silver chloride in 0.1 N-HC1 was placed and attached using an epoxy resin to make up an external reference electrode. As the external electrolyte 27, 0.02 mol NaCl and 0.005 mol NaHC03 were used. A poly-tetra-fluoroethylene film 20 cm in thickness was used as the polymer film 39. The sensor of the present invention shown in Figure 3 manufactured under the conditions as above mentioned showed an excellent performance and operability as shown in Table 2 when compared to the conventional sensor. In the second embodiment of the present invention, the measurement of H+ ion concentration changes (pH value changes) was successfully performed without using an internal electrolyte, similar to the first embodiment. Table 2 Properties of Sensor Manufactured according to the Present Invention Items Conventional Type Present Invention 1. Response time Conventional Type Present Invention (gas) (C0225% 10%) 2.Sensitivity (gas) potential change potential change (cho2 5%--+10%) 17 mV 17 mV 3.Performance Measurement impossible No change, when sensor because of disturbance continues to perform falls to potential excellently. Original potential not recovered when restored to original position. 4.Temperature At - 12 0C glass elect- No change at -200C at which sensor rode becomes broken. becomes broken due to freezing. 5.Impact resist- Breaks when dropped Does not break ance of glass from the height of when dropped from membrane of 1.5 m. height of 2 m. glass electrode Accordingly, the second embodiment has similar properties to those of the first embodiment, and since the heater 36 of the main electrode body 38 and the heater end portion 40 are screwed together with a screw 43, and the polymer membrane 39 of the membrane holder 41 is pressed against the glass electrode 30 by squeezing a thin film of the external electrolyte, the lead wires from the -anode and the cathode, the lead wires from the heat sensitive element and the feed wires for the heater are gathered together by a multicore cord connected to the main measurement device. In the conventional sensors where the top cover portion and the heater main body are separately constructed, the lead wire from the electrode which is led out of the top cover and the lead wire from the heat sensitive element of the heater main body and the feed wire to the heater had to have two separate cords, causing inconveniences in operation. However, the present invention facilitates connecting these output lead wires and the feed wires with one multicore cord, thereby enabling separation of the heater end portion 40 completely from the electrode main body 38. This removed all the disadvantages hitherto seen in the conventional assemblies where the screws had to be used. Figure 4 shows a cross sectional view of a transcutaneous C02 measurement sensor according to the third embodiment of the present invention. Referring to Figure 4, an H+ ion responsive glass membrane 45 is attached to the end of an annular member 46 made of an insulating material such as glass, ceramic, plastic or rubber by fusing or with an adhesive, to make up a glass electrode. A conductive coating 47 of a metal such as Au, Pt, Ag, etc. or a metallic salt such as AgCl, etc is formed on the inner surface of the glass membrane 45 by vacuum evaporation or ion plating. The metal coating may also be formed on the inner surface of the glass container by thermally fusing a metal or a metallic salt which has a lower melting point than that of the glass membrane. A particularly important component 48 of the present invention, namely a heater member made of a metal such as silver, copper, aluminium, etc. and having an excellent heat conductivity, houses a heater 49 and a heat sensitive element 50 and is controlled at a desired constant temperature. Figure 4 shows a construction where excellent electrical and thermal conduction may be maintained since the heater member adheres closely to the conductive coating 47 formed on the inner surface of the glass membrane 45. Accordingly, the conductive membrane 45 and the heater member 48 are joined together with a conductive adhesive agent, and the electrical potential of the conductive coating 47 is taken out by lead wire 51. It is naturally possible to use heater member 48, the surface of which has been insulated, to connect the lead wire 51 to the conductive coating 47. An annular shaped external reference electrode 52 comprising silver /silver chloride is provided around the outer circumference of the glass electrode. The glass electrode having a heating mechanism and the external electrode are fixed to an electrode holder 53 made of an insulating material, such as a plastics material or rubber. -A membrane holder 55 has a C02 transmittant and hydrophobic polymer film such as Teflons silicone rubber, etc. attached to the end thereof and it is disposable along with the polymer membrane 54. Between the glass membrane 45 and the polymer membrane 54 there is placed, as in the conventional art, an aqueous solution containing KC1, NaHC03J etc, as the C02 responsive electrolyte (of which the pH value varies depending on the C02 concentration). A pressure plate 56 is provided to press the polymer membrane 54 of the membrane holder 55 against the glass membrane by squeezing a film of the electrolyte 27. The pressure plate is removably screwed to the electrode holder 53. A specific example of the third embodiment of the present invention mentioned above is now explained in further detail. The glass membrane 45 composed of 25 wt% 2C 10 wt% of CaO and 65 wt% of SiO2 having a diameter of 8 mm and a thickness of 0.15 mm is fused to the end of a lead glass cylinder by soldering. Inside the glass container platinum is vacuum deposited. A heater member 48 made of copper is adhered to the inner wall of the container using a conductive adhesive agent to make up a glass electrode. Over the outer circumference of the glass electrode a silver ring the surface of which surface has been electrolyzed in 0.1 N-HC1 to transform it into silver chloride is fixed as an external reference electrode 52 using an epoxy resin. As the external electrolyte 27, 0.02 mol NaCl and 0.005 mol NaHCO3 were used. A 20 m thick Teflon @ filmwas used as a polymer membrane. The sensor according to the present invention manufactured under the conditions as above mentioned were confirmed to be excellent-both in performance and operability as shown in Table 3. Table 3 Items Prior Art Present Invention 1.Time until 25 min. 8 min. initial stab: lization 2.Response time 90% response 90% response (Gas) (C025%-510%) 37 sec. 36 sec. 3.Gas sensitivity Potential change Potential change (CO2 5%--- > 10%) 17 mV 17 mV 4.Correlation to 0.98 0.98 detected value in blood (correlation coefficient of transcutaneously measured value and value found in the blood sample) 5.Performance when Measurement not possible Excellent the sensor falls as the potential is performance disturbed. continues without Original potential not change. regained when restored change. to original position. 6. Temperature at Glass electrode breaks No change is which sensor at -12 C observed at becomes destroyed - 200C. due to freezing. 7.Impact resist- Breaks when dropped Does not break ance of the from the height of even when 1.5 m dropped from glass membrane the height of of glass electrode. 2.0 m. The sensor of the third embodiment also demonstrated the same effects as the first embodiment which enabled measurement of H+ ion concentration changes (pH changes) without using an internal electrolyte. In this case, further effects as hereinafter enumerated are achieved by having the heater body 48 inside the glass electrode: (1) The electrode reaches the measurement temperature in an extremely short period of time and accurately maintains the said temperature at a constant value thereafter because the pH responsive glass membrane directly contacts the heater member which is made of an excellent heat conductive metal. Therefore, there is no drift in the measurement value seen in the generated potential arising from the temperature variation at the electrode as often has often been observed in conventional products. (2) As the conventional product has a structure where an annular shaped heating member is attached around the glass electrode, and the diameter of the glass electrode must be made large, the skin temperature of the measurement portion does not rise quickly. Thus, it was impossible to expect a sensor with a good response. According to the present invention, the glass electrode itself heats the skin, and the diameter of the glass electrode may be arbitrarily determined to adapt it to any required performance. (3) The conventional product provided an annular shaped skin heating member over the outer circumference of the glass electrode, whereby the heated skin area inevitably increased. When the patient suffered a burn the scar was large. However, the product according to the present invention heats the skin only in about the same area as the cross section of the glass electrode. This means that the scar of a burn, is far smaller than those seen in patients for whom the conventional type was used. (4) Because the temperature effect of the electromotive force of the glass electrode is large, it is necessary to maintain the temperature of the glass electrode constant within +0.2 0C. The heating mechanism as employed in the present invention sufficiently meets this condition. As explained hereinabove, the present invention not only removes all the disadvantages of the conventional transcutaneous C02 sensor, but also offers an excellent transcutaneous C02 sensor with good performance and ease of operation. Figure 5 further shows a cross sectional view of a transcutaneous C02 sensor according to the fourth embodiment of the present invention. Referring to Figure 5 a pH responsive glass membrane 57 is attached to the bottom of-a support tube 58 to form a glass electrode. A conductive coating 59 is formed on the inner surface of the said glass membrane 57. A preamplifier 60 provided inside the glass electrode support tube 58 has a lead wire 61 for taking up the potential which is extremely short and connected to the conductive coating 59. It provides the preamplifier with a lower output impedance and the preamplifier 60 is connected to the main measuring device by lead wire 62. The external reference electrode 63 is disposed in such a way that it encircles the glass electrode, and the potential of the electrode 63 is connected to the preamplifier 60 which is connected to the main measuring device by the lead wire 64. The heat generating member 10 and the heat sensitive element 11 are the same as those used in the conventional art, and the lead wire 15a, the feeder line 15b from these member and element are connected to the main measuring device 69. A disposable membrane holder 67 has a stretched polymer membrane 68 at the end thereof. A specific example of the fourth embodiment of the present invention is explained in more detail below. A pH responsive glass membrane 57 having a composition of 25 mol% LiO2, 8 mol% BaO, and 67 mol% of SiO2 and a thickness of 120 pn was used in the experiment. The glass electrode support tube 58 comprises an insulated epoxy resin tube having an outer diameter of 6 mm, an inner diameter of 5 mm and a height of 8 mm. The membrane 57 was adhered to the bottom of the support tube 58 with a silicone adhesive, and on the inner bottom surface thereof was deposited a 7 /um thick coating of silver by vacuum deposition to form a conductive solid film 59. Metallic case type NOS FET was used as a preamplifier 60 (diameter 4 mm x height 4 mm), and the lead wire 61 for the preamplifier was adhered with a silver powder containing a conductive epoxy resin. A silicone rubber compound which hardened at normal temperatures was filled in the void 65 inside the glass electrode, except for the preamplifier and the lead wire, in order to increase and enhance the mechanical strength and insulating properties thereof. The circuit for the preamplifier comprises MOS type FET 66 as shown in Figure 6, and the output of the preamplifier is connected to the main measuring device by the lead wire 62. The ground potential terminal of the preamplifier is connected to the external reference electrode 63 which is maintained at the earth potential for shield purposes, and is connected to the ground potential terminal of the main measuring device by the lead wire 14. Table 4 shows the results of the performance comparison of the conventional sensor shown in Figure 1 and the sensor of the present invention shown in Figure 5. In the comparative experiment, poly-tetra-fluoroethylene membrane 13p:im in thickness were used for both the conventional assembly and the assembly of the present invention. An aqueous solution containing 0.005 mol NaHC03 and 0.02 mol NaCl was used as the electrolyte to be maintained between the polymer membrane and the glass electrode. Table 4 Comparison of Transcutaneous COn Measurement Assemblies Conventional Present invention Gas response Potential change, Potential change, sensitivity 16 mV 16 mV (CO2 5% - 10%) Noise level Potential change Potential change less than 2.3 mV less than 0.1 mV Drift Potential change, Potential change, less than less than 0.4 mV/H 0.1 mV/H Measurement values for human (mmHg) 1. Neonatal 30 32 (3 days old) 2. Infant (3 yr.old) Too active 35 measurement impossible 3. Adult 41 41 (healthy) 4. Adult 46 45 (pulmonary edema patient) A 40 T m thick lens spacer was inserted between the glass electrode and the polymer membrane as a spacer. The sensor was maintained at 43.50C andothe comparative experiment was conducted. As is clear from Table 4, the sensor according tc the fourth embodiment of the present invention is far superior to the conventional sensor as regards the noise level, with extremely small drifts, and stable measurement is guaranteed. As mentioned hereinbefore, according to the transcutaneous C02 measurement sensor, the following advantages in addition to those shown in Figure 2 are achieved: a) because the preamplifier is positioned in the glass electorde, the sensor may be reduced to a compact size amd and may easily be attached to the restricted measurement portion when being used with the premature and neonatal babies; b) as the preamplifier positioned in the glass electrode is enveloped by the external reference electrode 63, the electrode acts as a shield against the external electric field. The input lead wire for the preamplifier is extremely short, thereby remarkably reducing the static and the electromagnetic induction noise levels; c) as the preamplifier is positioned in the glass electrode which is maintained at a constant temperature, the temperature fluctation is reduced compared to that of the conventional product. Accordingly, a preamplifier is provided having less gain fluctuation and drift, thereby guaranteeing the stabilized measurement.

Claims: CLAIMS 1. A transcutaneous carbon dioxide measuring assembly integrally composed of three components, the first component comprising a top cover 24 centrally locating a glass electrode having an H+ ion sensitive glass membrane 17 at the end of a tubular member 18 made of an insulating material, a conductive coating 19 formed on the inner surface of the glass membrane 17 an external reference electrode 23 located around the glass electrode and lead wires 14 are connected to the conductive coating 19 and the external reference electrode 23, the second component comprising a heater member 28 which has a heater and a heat sensitive element and the third component comprising a membrane holder 25 having a polymer membrane 25 which is C02 permeable stretched between the ends thereof, the third component being disposed between the first component and the second component. 2. A transcutaneous carbon dioxide measuring assembly as claimed in claim 1 wherein the conductive coating 19 is formed from a metal. 3. A transcutaneous carbon dioxide measuring assembly as claimed in claim 2 wherein the metal is Au, Ag or Pt. 4. A transcutaneous carbon dioxide measuring assembly as claimed in claim 1 wherein the conductive coating 19 is formed from a metallic salt. 5. A transcutaneous carbon dioxide measurement assembly as claimed in claim 1 wherein the portion of the lead wire connected to the conductive coating is embedded in silicone rubber or an epoxy resin in the glass electrode. 6. A transcutaneous carbon dioxide measuring assembly comprising a body 38 provided with a glass electrode having an H+ ion sensitive glass membrane 30 at the end of Åa tubular member 31 made of an insulating material a conductive coating 32 formed on the inner surface of the glass membrane 30, an external reference electrode 35 located around the circumference of the glass electrode and lead wires 33 attached to the conductive coating 32 and the external reference electrode 35, a membrane holder 41 having a polymer membrane 39 stretched between the ends thereof located around the circumference of the external reference electrode 35 and the assembly being further provided with a heater member 36 comprising a heater 42 and a heat sensitive element 37, the membrane holder 41 being connected to the heater end portion 40 in such a way that the C02 permeable polymer membrane 39 of the membrane holder 41 is pressed onto the glass membrane 30 via an electrolyte. 7. A transcutaneous carbon dioxide measuring assembly comprising a glass electrode having an H ion sensitive glass membrane 45 at the end of a tubular member 46 made of an insulating material, a conductive coating 47 formed on the inner surface of the glass membrane 45, a heater 49 and a heat sensitive element 50 both being disposed inside the glass electrode and being adpated to contact the conductive coating both in thermal and electrical contact, an external reference electrode 52 located around the circumference of the glass electrode, and a membrane holder 55 having a C02 permeable polymer membrane 54 stretched between the ends thereof located around the circumference of the reference electrode, the polymer membrane being pressed onto the glass membrane 45 via an electrolyte. 8. A trancutaneous C02 measuring assembly wherein a conductive coating 59 is formed on the inner surface of a glass electrode having an H ion sensitive glass membrane 57 at the end of a tubular member 58 made of an insulating material, a preamplifier 60 being housed inside the glass electrode and an external reference electrode 63 being located around the circumference of the glass electrode.

Inventors: FUKAI, TAMOTSU OSAKA WORKS OF SUMITOMO ELECTRIC, HIRAMOTO, JUNICHI OSAKA WORKS OF SUMITOMO ELECTRIC, OHKAWA, SHINICHI OSAKA WORKS OF SUMITOMO ELECTRIC
Applicants: SUMITOMO ELECTRIC INDUSTRIES LIMITED
Application year: 1981
Main classification: A61B5
IPC codes: A61B5