WO1989007957A1 - Indicateur de co2 pour le positionnement de tubes tracheaux - Google Patents

Indicateur de co2 pour le positionnement de tubes tracheaux Download PDF

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Publication number
WO1989007957A1
WO1989007957A1 PCT/US1989/000796 US8900796W WO8907957A1 WO 1989007957 A1 WO1989007957 A1 WO 1989007957A1 US 8900796 W US8900796 W US 8900796W WO 8907957 A1 WO8907957 A1 WO 8907957A1
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WIPO (PCT)
Prior art keywords
indicator
detector
color
group
breath
Prior art date
Application number
PCT/US1989/000796
Other languages
English (en)
Inventor
Daniel B. Raemer
David R. Walt
Christianne Munkholm
Original Assignee
Brigham And Women's Hospital
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Brigham And Women's Hospital filed Critical Brigham And Women's Hospital
Publication of WO1989007957A1 publication Critical patent/WO1989007957A1/fr

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N31/00—Investigating or analysing non-biological materials by the use of the chemical methods specified in the subgroup; Apparatus specially adapted for such methods
    • G01N31/22—Investigating or analysing non-biological materials by the use of the chemical methods specified in the subgroup; Apparatus specially adapted for such methods using chemical indicators
    • G01N31/223—Investigating or analysing non-biological materials by the use of the chemical methods specified in the subgroup; Apparatus specially adapted for such methods using chemical indicators for investigating presence of specific gases or aerosols
    • 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
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/04—Tracheal tubes
    • A61M16/0402—Special features for tracheal tubes not otherwise provided for
    • A61M16/042—Special features for tracheal tubes not otherwise provided for with separate conduits for in-and expiration gas, e.g. for limited dead volume
    • 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
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/04—Tracheal tubes
    • A61M16/0488—Mouthpieces; Means for guiding, securing or introducing the tubes
    • 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
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A61M16/0816—Joints or connectors
    • A61M16/0841—Joints or connectors for sampling
    • A61M16/085—Gas sampling
    • 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
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/04—Tracheal tubes
    • A61M16/0402—Special features for tracheal tubes not otherwise provided for
    • A61M16/0411—Special features for tracheal tubes not otherwise provided for with means for differentiating between oesophageal and tracheal intubation
    • A61M2016/0413—Special features for tracheal tubes not otherwise provided for with means for differentiating between oesophageal and tracheal intubation with detectors of CO2 in exhaled gases
    • 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
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/20—Blood composition characteristics
    • A61M2230/202—Blood composition characteristics partial carbon oxide pressure, e.g. partial dioxide pressure (P-CO2)

Definitions

  • This invention relates generally to medical devices, and more particularly to a detection device for determining whether a tracheal tube is properly positioned within the trachea of a patient.
  • the operation of the Einstein detector device is broadly based upon a visual indication of the carbon dioxide concentration found in expired gases.
  • the technique described in the Anesthesio- locry article is based on the fact that gases expired from the lungs contain between 4% and 6% C0 2 whereas atmospheric air, which is expelled from the esophagus, has a negligible amount of CO2.
  • the device utilizes an adapter connected at one end to a mucous trap.
  • a tube connected to the trap is filled with a liquid indicator solution, and the catheter end of the trap is positioned to be well below the indicator fluid level.
  • the adapter is attached to the endotracheal tube, and expired gases are pumped through the indicator solution and are allowed to bubble therethrough. Utilizing a cresol red and phenolphthalein solution, a gradual color change from red to yellow occurs after several seconds upon proper tracheal intubation. No color change of the solution suggests esophageal intubation.
  • the Einstein detector has many drawbacks. Because the gas is bubbled through a liquid indicator, expired gas must be pumped through the liquid. This, of course, requires additional equipment not usually associated with a convention ⁇ al tracheal tube, such as a conduit or sample tube, a mucous trap, and of course, the liquid chemicals themselves. Liquid chemicals have their own inherent disadvantages; in particular, they are impractical because they can spill. Further, the change in color does not occur until three to five seconds after the expired gas has started bubbling through the mucous trap chamber.
  • the Einstein C0 2 detector also does not follow the breathing pattern of the patient. In other words, the indicator used by the Einstein C0 2 detector is not reversible on a time frame which would enable visual confirmation of breathing. Thus, the Einstein C0 2 detector is limited in its ability to provide an indication of proper or improper intubation. It does not actively detect breathing; it only detects place- ment.
  • U.S. Patent No. 3,373,735 to Gallagher teaches a device which indicates proper placement of a tube into a patient's stomach. After the tube is inserted into the stomach of a patient, a small amount of the stomach fluid is drawn into the tube to wet a color-change indi- cator. When the tube is properly inserted within the stomach of a patient, the indicator will turn red. If, however, the end of the tube has been improperly placed into the lungs, the indicator would remain a blue color.
  • This device of course. has nothing to do with the detection of respira ⁇ tion.
  • the face of the cell contains a small aperture which is sealed by a window which transmits virtually 100% of the infrared radiation which is absorbed by pure C0 2 which fills the cell.
  • Both the inner chamber of the cell and the face of the cell are fitted with thermistors which are con ⁇ nected to a sensing device for detecting the differences between the temperatures of the two thermistors.
  • the source and sensor are turned on and allowed to come to temperature equilibrium in an atmosphere virtually free of C0 2 , and the sensor is set to a chosen reference.
  • the radiation formerly absorbed by the gas in the cell is decreased, whereas that radiation absorbed by the face of the cell is affected only slightly.
  • the temperature differential allows the user to detect the content of carbon dioxide in the cell. While this device detects C0 2 , it is not colorometric, it is not rapid and is not positioned in a gas stream.
  • a porous impregnated surface contains a color-change indicator which changes in accordance with the carbon dioxide content.
  • This embodiment does not discuss the ability of the device to cycle from one color to another at a rate which _ is on the same order of magnitude as is the rate of breathing.
  • Guenther is not directed toward providing a C0 2 detector for use as a medical device.
  • U.S. Patent 3,068,073 to Stanford discloses a device for detecting the presence and determining the content of carbon dioxide in gases.
  • the gas containing an undetermined amount of carbon dioxide is passed through a solid reagent which includes alumina carrying thymol blue.
  • the reagent is confined within a transparent container and changes color by contact with carbon dioxide.
  • the quantity of carbon dioxide is determined by the length of time it takes for the color indicator to change the colors.
  • a rapid time change is preferred. Thus, such a time-consuming procedure would not be appropriate for medical applications.
  • the present invention is an intubation apparatus which includes a tube for receiving expiration gas.
  • a detector for visually indicat ⁇ ing whether a predetermined threshold concentration of carbon dioxide is present within the tube.
  • the detector is made up of indicator material which changes from one color to another and back to the first color in response to the presence then absence of a predetermined amount of C0 2 gas.
  • the indicator material includes a solid phase support and a pH sensitive dye. The dye may be adsorbed onto, covalently attached to, or entrapped within the solid phase support. To improve and enhance the response of the dye, a mixture of the pH sensitive dye and a phase transport enhancer is added to the solid phase suppor .
  • the detector may further contain a thin membrane disposed over the detector.
  • the invention also relates to methods for determining the proper placement of a tracheal intubation device comprising inserting a device comprising
  • an endotracheal apparatus which includes a tracheal tube defining a gas path; and (b) a C0 2 detector disposed within said tracheal apparatus at a location which is in the gas path of said tube and is visible when said endotracheal tube is inserted, said detector being capable of indicating whether a substantial concentration of C0 2 is present in said gas; and observing a color change of the indicator which indicates the presence of C0 2 in the respira- tory gas and thereby the proper placement of the endotracheal tube.
  • Figure 1 is a schematic illustration (not to scale) of a patient and of an intubation device according to the invention.
  • Figure 2 is a section view of an adapter and detector element of the invention.
  • Figure 3 is a cross-sectional view of the adapter and detector cut along line 3-3 of Figure 2.
  • Figure 4 is a schematic view showing one embodiment of how the indicator and support material of the invention is attached to a backing.
  • the present invention comprises a device for detecting whether a tracheal tube is properly positioned within the trachea.
  • Figure 1 illustrates a schematic (not to scale) representation of a patient desig ⁇ nated generally as 10, and of an endotracheal apparatus 26 using the present invention. Normal ⁇ ly, air is inhaled into the lungs of a patient 10 via either the nasal cavity 12 or the mouth 14. Similarly, C0 2 gas expired from the lungs is exhaled through the nasal cavity or the mouth.
  • the esophagus 16 which is oblong in cross section, connects the mouth with the stomach and provides a tube for ingestion of foods and liquids.
  • the trachea 18 is positioned in front of the esophagus 16 as shown in Figure 1 and connects the mouth and nasal cavity with the lungs.
  • the esophagus 16 and the trachea 18 are separated by a dividing wall 20, the corniculate.
  • the epiglottis 22 is a thin membrane of cartilage which is positioned behind the tongue 24 in front of the opening of the larynx
  • Forming the lower and back part of the cavity of the larynx is a ring-shaped piece of cartilage known as the cricoid membrane (not shown) .
  • a typical respiration or breathing circuit which will hereinafter be referred to as the "endotracheal apparatus" is shown generally as 26.
  • the endotracheal apparatus 26 is made up of a number of component parts which include a tube 28, an adapter 36, an elbow connector 40 and a bifurca ⁇ tion unit 37.
  • the tube 28 has an angled open end 30 which provides for easy insertion into the trachea of a patient 10 through either the mouth 14, the nasal cavity 12 or through a cricoid membrane puncture (not shown) .
  • Formed in the wall of tube 28 near the angled end 30 is a second opening 32.
  • a cuff 33 made of a thin plastic material which may be inflated to contact the sides of the tracheal wall.
  • the tube 28 is attached to the adapter 36 which in turn is attached to the elbow connector 40.
  • the bifurcation unit 37 provides a gas inhalation path 50 and a gas exhalation path 52.
  • the direction of gas flow is shown by the arrows labeled 41a and
  • Tracheal tube 28 has a centrally located primary passage for allowing oxygen and other gases to be passed into the lungs.
  • a conventional secondary passage (not shown) connecting cuff 33 to a syringe may also be provided to allow inflation of the cuff 33. This enables the cuff 33 to contact the inside of the trachea 18, thereby preventing gases from escaping through the mouth and nose of the patient.
  • the present invention provides a device, such as a detector 38, which enables the user to determine whether the endotracheal tube 28 is properly placed in the trachea 18.
  • Detector 38 in a preferred embodiment, is located in adapter 36 and includes means that respond to a minimum concentration of carbon dioxide.
  • the response preferably takes the form of a visually observable state change, such as changing from one color to another.
  • the principle of operation is based on the fact that gas expired from the lungs has a high concentration of C0 2 while gas which is inspired, driven to the stomach and returned through the esophagus has an extremely low concentration of C0 .
  • the detector 38 By placing the detector 38 contiguous with gases expired from patient 10, it is possible to chemically determine if the concentration of carbon dioxide in gas expired through the endotracheal tube exceeds a minimum accepted value. If it does, the detector, which includes a pH sensitive dye, will change from one color to another thus visually indicating to the attending physician or other personnel the presence of C0 2 . This in turn means that the endotracheal tube is properly positioned within the trachea rather than the esophagus. The detector 38 may also cycle between one color and another in response to breathing, i.e., on a breath-by-breath basis.
  • a detector 38 is provided in the endotracheal apparatus 26 and is positioned so that gases expired from the patient 10 will make contact with the detector 38.
  • the detector 38 may be installed at various places in the respiratory gas path. Although in a preferred embodiment of the invention the detector 38 is positioned on the inside wall of the adapter 36, it may also be located in the portion of the tube 28 which is not within patient 10, the elbow adapter 40, the bifurcation unit 37 or at a location even further downstream. It is preferred, however, that -li ⁇
  • the detector be located as close to the source of exhalation gas as possible.
  • the detector 38 must be seen by an observer or opera- tively connected to a device which may be read by an observer.
  • the part of the endotracheal apparatus 26 housing the detector 38 is made of a transparent material so that the detector 38 can be seen by an observer.
  • the detector 38 includes a solid indicator material which alleviates the problems associated with a liquid indicator and enables the detector 38 to be positioned in a conventional endotracheal apparatus without having to pump expiration gases through a liquid.
  • indicator materials and accessory materials have been found for use in the detector 38 which change color in a time frame which corresponds to that of inhalation and exhalation of the patient 10. This is a major advantage in that it enables breath by breath detection of both proper intubation and breathing.
  • FIG 2 is an enlarged view of adapter 36 shown in Figure 1 while Figure 3 is a cross-section of Figure 2.
  • This adapter has a first end 60 which, is adapted to be connected to tube 28.
  • the adapter 36 also has a second end 62 which is typically of larger diameter than the first end. This second end 62 is adapted to be connected to the L-shaped connector 40.
  • the precise configurations of the adapter 36 and the other components of the endo- tracheal tube are not particularly important to the present invention.
  • the detector 38 is positioned in the normal stream of exhaled gases and is visible to an observer.
  • the detector 38 can be made of a number of different materials as will be discussed later. As seen in Figure 3, the detector 38 may follow the curve of adaptor 28 thereby not affecting the flow of gases through adapter 28.
  • Figure 4 shows a cross section schematic view of the detector 38.
  • the detector is shown to be flat. In a preferred embodiment, however, the detector conforms to the shape of the inner wall of adapter 36 as mentioned above.
  • a thin layer of adhesive 64 is applied to a backing member 65 such as a strip of transparent polymeric sheet.
  • Indicator material 68 is liberally sprinkled onto the adhesive, the excess is removed and the system is left to dry.
  • the detector 38 having indicator material 68 is then inserted into the adapter 36 so that gas passing through adapter 36 will be contiguous with the indicator material 68.
  • the indicator material 68 includes a support material such as a porous glass and a pH sensitive dye which will change colors when in contact with C0 2 .
  • Various backings in various shapes and sizes may be used to practice the invention.
  • the material, size, shape, and physical properties of the backing structure are not critical to the device's operation.
  • the adapter 36 itself out of a material such as a controlled pore glass (CPG) tube, the need for a separate, indepen ⁇ dent backing member or a separate support material may be eliminated.
  • CPG controlled pore glass
  • the attachment of the support material and indicator to the backing may be accomplished with various glues and adhesives which include, but are not limited to, epoxy, cyanoacrylate, silicone rubber, and tape. Any glue or adhesive which does not interfere adversely with the indicator may be used to practice the invention. If the porous support is made into a plate or tape of the appro ⁇ priate dimensions, no glue or adhesive may be required.
  • the detector 38 is covered with a thin polymeric membrane 70 as shown in Figure 4.
  • the detector material may be protected from undesirable sources of contamination such as water, stomach acids, mucus, and other undesirable liquids.
  • Such specificity may be achieved by selecting a polymeric membrane which exclusively passes gasses but not liquid.
  • a membrane with such a characteristic By selecting a membrane with such a characteristic, a high degree of selectivity can be achieved by using a sensitive but otherwise unselective indicator material 68.
  • a preferred polymeric membrane is polytetra- fluorethylene (PTFE) membrane, also known as Gortex, which freely allows the passage of C0 2 through the membrane, but does not allow liquid water to pass.
  • PTFE polytetra- fluorethylene
  • Such a Gortex membrane may have a pore size of 1 or 3 ⁇ M or any other suitable size.
  • Other suitable membranes may be selected by one of ordinary skill in the art which allow C0 2 to pass without undue experimentation.
  • layered chemistry is used to form the detector 38.
  • layers of polymer bound chemistry are prepared to tailor the response to the system. For instance, a selective membrane polymer would cover a layer of C0 2 indicator material which would cover a layer of material having a high affinity for C0 2 . C0 2 gas would penetrate the selective membrane polymer and pass through the indicator material layer on its way to the high C0 2 affinity layer. In this way the color change of the indicator layer would be transitory and result in a more rapid system response.
  • Materials which have a high affinity for C0 2 include, but are not limited to, calcium oxide (CaO) , lithium hydroxide (LiOH) , alkali carbonates, ethanolamine and the like. See Kirk-Othmer, Concise Encyclopedia of Chemical Technology. Wiley-Interscience, New York (1985) , page 213.
  • ethanolamine is used to absorb C0 2 , it may be adsorbed upon or entrapped within a solid phase support.
  • a drying agent or desiccant may be used to absorb any liquid present in the breathing circuit.
  • a desiccant may be either added to the indi ⁇ cator material 68 or placed between indicator material 68 and the membrane 70.
  • desiccants may include any of those known to those skilled in the art, for example, calcium sulfate, calcium chloride, magnesium sulfate, molecular sieves, sodium sulfate, calcium oxide, alumina, silica gel or potassium carbonate. See Gordon, A.J. , et al..
  • the desiccant may either produce a chemical reaction to form a new compound (for example, Ca(OH) 2 from CaO) or form a hydrate.
  • the detector may comprise a physical desiccant such as a piece of filter paper placed between indicator material 68 and membrane 70.
  • the detector 38 turns purple on inhalation and yellow on exhalation.
  • the speed of response is adequate enough so that even at rapid breathing rates each inhalation and exhalation is indicated. It is of course important that anesthetic gases and agents, oxygen and water vapor do not provide a perceivable response in the material forming the detector 38.
  • the indicator can be shaped to spell "C0 2 " or "carbon dioxide” so that upon changing from a light color to a dark color it can be immediately recognized by the user that C0 2 is in contact with the indicator.
  • the device may also be used in a device for intubation of the esophagus using the same principles of the endotracheal tube described above, but of course by observing no color change.
  • Another adaption of the invention is to detect the color change of the detector 38 by means other than visual observation.
  • every color corresponds to one or more different wave ⁇ lengths of light.
  • the invention is not limited to changes which are detected by observa- tion with the unaided eye.
  • a change in "color" from one wavelength to another, though not detectable by the unaided eye may be detected by electronic means or an optical detection scheme.
  • the electronic means could be connected to an alarm, a light bulb or the like.
  • the respiratory gas composition may be continuously monitored without the need for continuous observa ⁇ tion of the detector.
  • the color change may be detectable only through the use of transfor- mation equipment such as a blacklight. It can be seen that the term "color,” as used throughout this disclosure, is not limited to wavelengths which are detectable by the unaided eye.
  • one of the key features of the present invention is the ability to respond rapidly which gives it the ability to completely and reversibly change color in response to a change from inhalation to exhalation and back to inhala ⁇ tion.
  • One aspect of the invention is the accelera- tion of the exchange of C0 2 to and from a liquid phase pH sensor. This is accomplished in accord ⁇ ance with the invention by the addition of a phase transport enhancer which may comprise a quaternary ammonium, phosphonium or pyridinim salt mixed with or added to a layer of pH sensitive dye.
  • a detector comprising a pH-sensitive dye and a phase transport enhancer is able to change color with each breath taken by the patient. This ability to quickly change color with each breath allows the anesthesiologist to confirm that the endotracheal tube is properly placed in the trachea and that the patient is exchanging oxygen for carbon dioxide.
  • the preferred chemical indicator comprises a porous glass support to which a pH sensitive dye, water, and a phase transport enhancer are adsorbed.
  • the indicator may further comprise a buffer.
  • the support used may be a material such as an aminopropyl controlled pore glass particles.
  • 0.20ml of concentrated cresol red dye solution is added to 2ml TBAH prepared as above. This solution is pipetted on to the CPG while positioned on a vacuum filtration apparatus. This sample is dried for several hours in air.
  • the resulting granules are sensitive to C0 2 gas and turn from purple to yellow upon exposure within a fraction of a second.
  • the color response is completely and rapidly reversible upon exposure to non-C0 containing gas.
  • the support material may be any material upon which a dye can be adsorbed or covalently attached.
  • Various porous and non-porous supports may be used as the support including controlled pore glasses, ion exchange resins, celluloses, collagens, polymerics such as polyacrylamides, polymethacryl- ates, polystyrenes, polylysines, polyurethanes, polyesters, and polysiloxanes.
  • Such supports are well known to those of ordinary skill in the art and may be prepared according to any methods commonly used.
  • the properties of the surface area, ability to adsorb the dye, and lack of a strong hydrophobicity will affect the performance of the indicator and thus, can be selected to improve the indicator function.
  • This activa ⁇ tion chemistry may include treatment of glass surfaces with silanizing agents as:
  • silanizing agents may be used, includ ⁇ ing, but not limited to, those listed in Table 1.
  • Activated surfaces may also be prepared by plasma deposition.
  • Furukawa, T., et al.. SIA. Surf. Interface Anal. 4:204-244 (1982) discloses methods for forming a layer of aluminum oxide by plasma deposition followed by absorption of aminophenyltrimethoxysilane.
  • See also U.S. patent application, Serial No. 707,912, filed February 11, 1977 (available from the NTIS) discloses plasma polymer deposition to give a polyallylamine surface coating.
  • the pH sensitive dye, and optionally the quaternary ammonium salt may be entrapped within a hydrogel polymer.
  • Suitable hydrogel polymers are those which readily absorb C0 2 and water. Suitable hydrogel polymers include, but are not limited to, polymers such as polyacryl ⁇ amide and acrylamide-methylene bisacrylamide copolymer. The polymer may also contain a cross ⁇ linking agent having at least two polymerizable double bonds.
  • Cross-linking agents having at least two polymerizable double bonds include (i) di- or polyvinyl compounds such as divinylbenzyl and divinyltoluene; (ii) di- or poly-esters of unsatu- rated mono- or pol carboxylic acids with polyols including, for example, di- or triacrylic acid esters of polyols such as ethylene glycoi, trimethylol propane, glycerine, or polyoxyethylene glycols; (iii).
  • bisacrylamides such as N,N-methyl- enebisacrylamide
  • carbamyl esters that can be obtained by reacting polyisocyanates with hydroxyl group-containing monomers
  • di- or polyallyl ethers of polyols di- or polyallyl esters of polycarboxylic acids such as diallyl phthalate, diallyl adipate, and the like
  • esters of unsaturated mono-or polycarboxylic acids with monoallyl esters of polyols such as acrylic acid ester of polyethylene glycoi monoallyl ether
  • di- or triallyl amines di- or triallyl amines.
  • An optional component of the reaction mixture used to prepare the pH-sensitive dye-entrapped polymer is a free radical initiator.
  • an initiator may comprise any conventional polymeriza ⁇ tion initiator material including, for example, peroxygen compounds such as sodium, potassium and ammonium persulfates, caprylyl peroxide, benzoyl peroxide, hydrogen peroxide, cu ene hydroperoxides, tertiary butyl diperphthalate, tertiary butyl perbenzoate, sodium peracetate, sodium percarbonate and the like.
  • Conventional redox initiator systems can also be utilized. Such systems are formed by combining the foregoing peroxygen compounds with reducing agents such as sodium bisulfite, L- ascorbic acid or ferrous salts.
  • the initiator material can comprise up to about 5 mole percent based on the total moles of polymerizable monomer present. More preferably the initiator comprises from about 0.001 to 0.5 mole percent based on the total moles of polymerizable monomer in the reaction mixture.
  • Various other treatments of the support surface may be required to optimize its properties. These include adjustment of the pore size and composition of the support, preconditioning the surface pH with buffers or other solutions, changing the ionic charge, and controlling the ionic strength of the dye and conditioning solu- tions.
  • Various dyes are available which change color in response to changes in pH or the presence of C0 2 .
  • Any dye which changes color in response to a change in local pH which can be adsorbed to a porous surface such as controlled pore glass particles, and which has a pK a lower than the pH of a given support surface can be utilized to practice the invention.
  • Table 3, shown below, is a non- exhaustive list of dyes which have the above properties. Combinations of these dyes may also be used to optimize the contrast of the color change to the pH change.
  • One example of such a mixture is the combination of thymol blue and phenolphthalein.
  • the surface of the support material and the environment of the dye and support must have a local pH in the appropriate range for a C0 2 detector reaction to occur.
  • Monobasic and dibasic phosphate buffers, Mcllvaine buffers, etc. may be used to achieve this condition.
  • the concentration of the buffer must be low enough so that it does not prevent the pH change induced by C0 2 .
  • Non- buffering acids and bases such as HCl and NaOH can also be applied.
  • Phase transport enhancers which may comprise quaternary ammonium, phosphonium or pyridinium salts, contained as part of the dye solution applied to the support surface, enhance response of the dye to C0 2 gas as well as alter the color and visibility of the indicator.
  • R l , R 2 , R and R 4 are selected from the group consisting of C 1 -C 12 alkyl, triphenylmethyl, phenyl, naphthyl and benzyl, c l ⁇ c 4 substituted alkyl wherein the sub ⁇ stituent is a C ⁇ -C 4 alkyl or phenyl group,
  • Y ⁇ is an anion selected from the group consisting of hydroxide, fluoride, chloride, bromide, iodide, carbonate and tetrafluoroborate.
  • phase transport enhancers include pyridinium salts of the formula (II) :
  • R 5 is selected from the group consisting of C 1 -C ⁇ 2 alkyl and benzyl; and Y is an anion selected from the group consisting of hydroxide, fluoride, chloride, bromide, iodide, carbonate, and tetra ⁇ fluoroborate.
  • phase transport enhancers which are useful in the practice of the invention are listed in Table 4.
  • the C0 2 indicator disclosed has many other potential uses.
  • the C0 2 indicator could be attached to an object to serve as a hand-held life monitor. The object would be held above the mouth or nose of an accident victim to determine whether the victim was breathing.
  • the indicator could be mounted in the valve assembly of a manual bag resuscitator.
  • the indicator would help to deter ⁇ mine the success of the resuscitation attempt.
  • the indicator changes color at C0 2 > 5%
  • the indicator of the present invention could be used during anesthesia to detect malignant hyperthermia, a disease triggered by anesthetic drugs which leads to a hypermetabolic rate.
  • the indicator of the present invention could also be used in gas masks to determine if an unconscious worker or soldier was alive without having to remove the mask.
  • Another possible adaptation of the invention is to quantify the amount of C0 2 passing through an endotracheal tube. This can be done by providing a plurality of indicators, each of which respond to different concentrations of C0 2 .
  • Indicators which respond to different concentrations of C0 2 may be prepared by combining the pH-sensitive dye with various buffers which have a pH higher than the pK a of the buffer. The larger the difference between the pH of the buffer and the pK a of the pH-sensi- tive dye, the higher is the concentration of C0 2 which is required to cause a reduction in the pH of the support material and, thereby, a change in color.
  • the plurality of indicators may constitute, for example, a series of bands in defined locations on the detector. The bands may be marked, for example, with the percent of atmospheric C0 2 which is necessary to cause a color change of the detector.
  • a detector comprising a plurality of detectors can be used advantageously to estimate the pC0 2 of the blood without withdrawing a blood sample.
  • Tetrabutylammonium hydroxide was obtained from the Aldrich Chemical Company (Milwaukee, WI) .
  • silica gel samples were pretreated with a variety of bases to overcome acidic influence on the dye behavior. Previous dye treatments on silica all failed due to acidic effect of the silica on the dye.
  • the four bases comprised 5 M NaOH, 1 M NaOH, 0.05 M phosphate and 15% aqueous tetra t-butylammonium hydroxide (TBAH) , a phase transfer catalyst. After presoaking in one of the four bases, the silica gel was then treated with aqueous bromothymol blue. Samples that were treated with NaOH were deep blue and changed color to green-blue after a 50 sec. exposure to 99% C0 2 . The color change was not reversible.
  • TBAH aqueous tetra t-butylammonium hydroxide
  • the samples comprising 0.05 M phosphate behaved in the same way but changed color from light green to yellow.
  • the TBAH sample changed from blue to yellow after 50 sec. exposure to 99% C0 2 , and unlike the other samples, the color reverted to the original blue in the absence of C0 2 within approximately 1-2 min. Exposure of these samples to 5% C0 2 did not produce a color change.
  • Phenol red was incorporated into five samples of crosslinked acrylamide polymer at various concentrations.
  • the polymer was pulverized then rinsed with phosphate buffer, pH 8.94. Exposure to 99% C0 2 produced a color change from red to yellow in 20 sec. The color reverted back to yellow within 4 min. Exposure to 5% C0 2 produced a change from red to orange in 2.5 min. The color reverted back to red in the absence of C0 2 after many minutes. Addition of NaHC0 3 to the indicator material slightly increased response time and slowed recovery time.
  • Silica gel was treated with 1 M TBAH, pH 13.10, then soaked in aqueous bromothymol blue. Exposure to 99% C0 2 caused the blue silica gel to change to green-yellow within 25 sec. The color reverted back to blue in the absence of C0 2 within several minutes. The color contrast was signi ⁇ ficant; however, the response time was still slow.
  • CPG Alkylamine controlled pore glass
  • Bromothymol blue was adsorbed onto 2 CPG samples.
  • a first sample was pretreated with phosphate buffer (pH 6.6).
  • the second sample was untreated. Both samples became deep blue and changed color to blue-green on exposure to 99% C0 2 .
  • the change was rapid and reversible. Exposure to 5% C0 2 produced no color change.
  • This preparation was inferior to the preceding experiment for two reasons: 1) there was little color contrast in the colorimetric response, and 2) there was no sensi ⁇ tivity to low C0 2 concentrations.
  • the dye cresol red was applied onto amino CPG that had been pretreated with phosphate buffer. Exposure to 99% C0 2 produced a color change from purple to red. Although the color change was rapid, the contrast was poor. Exposure to 5% C0 2 produced no effect.
  • Cresol red was applied to two samples of amino CPG.
  • the first sample was pretreated with 0.1 M phosphate buffer at pH 8.0 to give crimson colored CPG which did not respond to 99% C0 2 .
  • the second sample was pretreated with 0.5 M TBAH solution, followed by treatment with cresol red, to produce CPG which was deep purple-green. This sample reversibly changed to clear-yellow on exposure to 5% C0 2 . This sample also responded reversibly to the presence and absence of respiratory C0 2 .
  • Cresol red was applied to three samples having the following pretreatments: 1) 0.5 M TBAH, pH 8.6, 2) 0.4 M NaOH, pH 8.6, and 3) 0.5 M phosphate buffer, pH 8.6. Each sample was then treated with the same cresol red solution, using the same application technique. After drying, sample 1) was purple and changed reversibly and rapidly to yellow upon exposure to 5% C0 2 . Sample 2) was crimson and changed to yellow upon exposure to 5% C0 2 . However, the response of sample 2) was not reversible over time. The colorimetric effect disappeared. Sample 3) behaved the same as sample 2).
  • the dye phenol red was added to a solution of TBAH and pH adjusted to 8.0. Three dye concentra- tions were prepared. The solutions were then pipetted onto amino CPG. When dry, all samples responded rapidly and reversibly to the presence and absence of 5% C0 2 . After one week, the response was still active. The colorimetric range of these samples were purple to yellow. These colors are uncharacteris ⁇ tic of the acid-base spectrum of phenol red. Thus, application of TBAH and cresol red solutions seems to perturb the normal color spectrum associated with this dye.
  • the dye xylenol blue was added to TBAH solution and applied to amino CPG to produce a material that changed from turquoise to yellow upon exposure to 5% C0 2 . This color change was rapid and reversible.
  • the dye curcumin was added to a TBAH solution and applied to amino CPG to produce a material that changed color from hot pink to orange yellow upon exposure to 5% C0 2 . After 8 days, the colors had lost much intensity and response to C0 2 .
  • Sections of glass tubing having controlled pore glass deposited on the interior surface were activated with aminopropyltriethoxysilane.
  • the tubing was then treated with a solution comprising xylenol blue and TBAH, pH 12.0.
  • the samples changed color from blue to yellow reversibly in the presence and absence of C0 2 , but not as rapidly as did the CPG sample.
  • a disadvantage of this preparation was that the dye was not . permanently adsorbed and tended to leach off the CPG upon standing.
  • xylenol blue was attached by a diazo linkage to produce a colorimetric glass that was deep blue in aqueous NaOH and deep red in aqueous HCl. The material did not show response upon exposure to C0 2 with or without TBAH treatment.
  • Example 15 The experiment of Example 15 was repeated using the arylamine glass from Pierce to produce a glass that was purple in aqueous NaOH and deep orange in aqueous HCl. The material did not respond upon exposure to C0 2 , with or without TBAH treatment. This experiment was repeated using bromocresol purple, rosolic acid, xylenol blue and dilute cresol red to produce colorimetric glasses which did not respond to C0 2 .
  • Cresol red was brominated with N-bromo- succinimide and was then coupled to amino glass.
  • the sample was brown in aqueous NaOH and orange in aqueous HCl.
  • Application of TBAH resulted in a color change to forest green which changed to olive green upon exposure to 5% C0 2 .
  • the color response did not persist.
  • Cresol red was covalently coupled to arylamine
  • CPG by a diazo linkage.
  • the sample was deep blue in aqueous NaOH and orange in aqueous HCl, but did not respond upon exposure to C0 2 , with or without the addition of TBAH solution.
  • Phenol red was immobilized by polymerization to amino CPG that had been derivatized with acryloyl chloride to produce a material that was deep crimson in aqueous NaOH and orange in aqueous HCl.
  • the sample did not respond upon exposure to C0 2 after treatment with TBAH and pH adjustments.
  • Phenol red was immobilized by polymerization to silica gel which was derivatized with methacryl- oxypropyltrimethoxysilane to produce a glass that was light red in aqueous NaOH and yellow in aqueous
  • Phenolphthalein was immobilized to amino CPG that was derivatized with acryloyl chloride to produce a glass that was intensely purple in aqueous NaOH and colorless in aqueous HCl. Exposure to 5% C0 2 caused a change from purple to beige which reversed to pale pink in the absence of C0 . The response disappeared after several cycles. Further addition of TBAH did not restore the color response.
  • Example 23 Phenolphthalein was immobilized to amino CPG that was derivatized with acryloyl chloride to produce a glass that was intensely purple in aqueous NaOH and colorless in aqueous HCl. Exposure to 5% C0 2 caused a change from purple to beige which reversed to pale pink in the absence of C0 . The response disappeared after several cycles. Further addition of TBAH did not restore the color response.
  • Thymol blue, bromothymol blue and pheno- phthalein were each adsorbed onto diethylaminoethyl cellulose, an anion exchange resin.
  • the material showed intense colorimetric behavior in solution, but did not response upon exposure to C0 2 ,
  • Phenol red and bromothymol blue were each immobilized to amino CPG derivatized with acryloyl chloride.
  • the phenol red glass was magenta in aqueous NaOH and yellow in aqueous HCl.
  • the bromothymol blue glass was green-blue in aqueous NaOH and yellow in aqueous HCl.
  • the samples did not respond to C0 2 with or without TBAH.
  • the dye Orange I (Tropoelin 000) was coupled to amino CPG by conversion of the sulphonate of Orange I to the sulphonyl chloride followed by treatment with amino CPG to produce a glass that was rust colored in aqueous HCl and deep red in aqueous NaOH. The color contrast was too weak to enable determination of pKa or presence of C0 .
  • the dye neutral red was coupled to amino CPG with cyanuric chloride to produce a glass that was brown in aqueous NaOH and red brown in aqueous HCl.
  • the color contrast was too small for use as a detector of C0 2 •
  • Uncoated CPG was derivatized with methacryl- oxypropyl trimethoxysilane and then reacted with phenol red to produce a glass that was crimson in aqueous NaOH and orange in aqueous HCl. Exposure to 99% C0 2 produced a color change from pink to yellow (20 sec.) which reversed to pink in the absence of C0 2 within minutes. This indicator material worked only when the material was wet.
  • Thymol blue was immobilized to uncoated CPG as described in Example 28 to produce a glass that was orange in aqueous NaOH and scarlet in aqueous HCl. This material did not respond upon exposure to 99% C0 2 . Addition of TBAH caused a color change to green-yellow. However, the TBAH material did not respond upon exposure to 99% C0 2 .
  • a cresol red glass was prepared by diazo attachment. This material was deep blue in aqueous NaOH. After treatment with TBAH, the sample showed a colorimetric response upon exposure to 99% C0 2 which comprised grey-green lightening to a salmon hue. After several, cycles, the response faded, but was partially restored by retreatment with TBAH. Eventually C0 2 sensitivity disappeared. A third treatment with TBAH produced a material that gave a slight colori etric response to 99% C0 2 but even less response to 5% C0 2 . This experiment indicated that TBAH could influence covalent attachment and have a restorative effect on colorimetric behavior.
  • the sample was then placed on a glass slide and enclosed with gortex material.
  • the resulting detector responded to 5% C0 2 with no loss of color contrast or response time.
  • Amino CPG was treated with the four pH dye solutions described in Example 32 containing TBAH dissolved in the dye solution. All samples changed color from purple to vivid yellow upon exposure to 2% C0 . The sample showed lightening of color upon exposure to 1% C0 2 . The response is immediate and recovery is extremely rapid. This one step application is the easiest and has possibly produced the best samples.
  • Samples were also prepared containing benzyl- trimethylammonium hydroxide at pH 13.0 and 9.0.
  • the pH 13.0 sample changed color from dark purple to grey- yellow upon exposure to 5% C0 2 .
  • the pH 9.0 sample changed color from mauve to pink yellow upon exposure to 1% C0 2 .
  • Samples were also prepared containing tetra- ethylammonium hydroxide at pH 13.0 and 8.8.
  • the pH 13.0 sample changed color from dark reddish-purple to yellow upon exposure to 10% C0 2 and to mauve upon exposure to 5% C0 .
  • the pH 8.8 sample changed color from mauve to yellow-pink upon exposure to 2% C0 2 .

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Pulmonology (AREA)
  • General Health & Medical Sciences (AREA)
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  • Heart & Thoracic Surgery (AREA)
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Abstract

L'invention se rapporte à un détecteur de CO2 dans les gaz dégagés par le processus respiratoire, et notamment à des instruments médicaux contenant un détecteur de CO2 servant à détecter le CO2 dans les gaz dégagés par le processus respiratoire. L'invention se rapporte également à un procédé permettant de déterminer l'emplacement correct d'un instrument d'intubation, consistant à introduire un tube trachéal (28) contenant un détecteur de CO2, et à observer si ledit détecteur change de couleur en réaction à la présence de CO2 dans les gaz expirés. Les détecteurs de CO2 ci-décrits (38) comprennent un colorant sensible au pH (68) et un support à phase solide (64). Ces détecteurs de CO2 peuvent comprendre également un agent améliorant le transport de phase qui permet au détecteur de réagir simultanément à la présence ou à l'absence de CO2 dans les gaz expulsés à chaque expiration.
PCT/US1989/000796 1988-02-26 1989-02-27 Indicateur de co2 pour le positionnement de tubes tracheaux WO1989007957A1 (fr)

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Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1991005252A1 (fr) * 1989-09-29 1991-04-18 Abbey Biosystems Limited Detecteur de dioxyde de carbone
US5279289A (en) * 1991-10-15 1994-01-18 Kirk Gilbert M Resuscitator regulator with carbon dioxide detector
US5323774A (en) * 1992-04-30 1994-06-28 Dragerwerk Ag Breathing mask with an indicator signalling penetration of a toxic substance into the mask
US5375592A (en) * 1993-04-08 1994-12-27 Kirk; Gilbert M. Carbon dioxide detector and shield
WO1997014464A1 (fr) * 1995-10-20 1997-04-24 Nellcor Puritan Bennett Incorporated Dispositif endotracheal a usage pediatrique
WO2000002845A1 (fr) * 1998-07-11 2000-01-20 Sensormetrix International Limited Sels d'ammonium quaternaire, film polymere les renfermant et dispositif colorimetrique
WO2000002844A1 (fr) * 1998-07-11 2000-01-20 Sensormetrix International Limited Sels d'ammonium quaternaire, film polymere les contenant et dispositif a colorimetre
FR2782646A1 (fr) * 1998-09-02 2000-03-03 Smiths Industries Plc Appareil respiratoire comportant un ensemble indicateur
US6123075A (en) * 1991-10-15 2000-09-26 Mallinckrodt, Inc. Resuscitator regulator with carbon dioxide detector
DE10025202A1 (de) * 2000-05-20 2001-11-29 Messer Austria Gmbh Gumpoldski Gasdosiergerät mit Katheter
WO2012030232A1 (fr) * 2010-09-03 2012-03-08 Fisher & Paykel Healthcare Limited Indicateur de respiration
WO2012046087A1 (fr) * 2010-10-05 2012-04-12 Symeon Grigoriou Tube endotrachéal comportant un indicateur de ph
FR3034870A1 (fr) * 2015-04-13 2016-10-14 Commissariat Energie Atomique Capteur chimique de type optode, son procede de preparation et ses utilisations
US10175254B2 (en) 2013-07-16 2019-01-08 Palo Alto Health Sciences, Inc. Methods and systems for quantitative colorimetric capnometry
WO2020109915A1 (fr) 2018-11-27 2020-06-04 Fisher & Paykel Healthcare Limited Indicateur d'haleine

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4728499A (en) * 1986-08-13 1988-03-01 Fehder Carl G Carbon dioxide indicator device
US4734125A (en) * 1986-01-15 1988-03-29 Bayer Aktiengesellschaft 5-acylamido-1-aryl-pyrazoles, composition containing them and herbicidal method of using them

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4734125A (en) * 1986-01-15 1988-03-29 Bayer Aktiengesellschaft 5-acylamido-1-aryl-pyrazoles, composition containing them and herbicidal method of using them
US4728499A (en) * 1986-08-13 1988-03-01 Fehder Carl G Carbon dioxide indicator device

Cited By (32)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5472668A (en) * 1989-09-29 1995-12-05 Abbey Biosystems Limited Carbon dioxide monitor
WO1991005252A1 (fr) * 1989-09-29 1991-04-18 Abbey Biosystems Limited Detecteur de dioxyde de carbone
US5679884A (en) * 1991-10-15 1997-10-21 Kirk; Gilbert M. Resuscitator with carbon dioxide detector
US5279289A (en) * 1991-10-15 1994-01-18 Kirk Gilbert M Resuscitator regulator with carbon dioxide detector
US5456249A (en) * 1991-10-15 1995-10-10 Kirk; Gilbert M. Resuscitator with carbon dioxide detector
US6427687B1 (en) 1991-10-15 2002-08-06 Mallinckrodt, Inc. Resuscitator regulator with carbon dioxide detector
US6123075A (en) * 1991-10-15 2000-09-26 Mallinckrodt, Inc. Resuscitator regulator with carbon dioxide detector
US5323774A (en) * 1992-04-30 1994-06-28 Dragerwerk Ag Breathing mask with an indicator signalling penetration of a toxic substance into the mask
US5517985A (en) * 1993-04-08 1996-05-21 Kirk; Gilbert M. Carbon dioxide detector and shield
US5375592A (en) * 1993-04-08 1994-12-27 Kirk; Gilbert M. Carbon dioxide detector and shield
WO1997014464A1 (fr) * 1995-10-20 1997-04-24 Nellcor Puritan Bennett Incorporated Dispositif endotracheal a usage pediatrique
WO2000002845A1 (fr) * 1998-07-11 2000-01-20 Sensormetrix International Limited Sels d'ammonium quaternaire, film polymere les renfermant et dispositif colorimetrique
WO2000002844A1 (fr) * 1998-07-11 2000-01-20 Sensormetrix International Limited Sels d'ammonium quaternaire, film polymere les contenant et dispositif a colorimetre
FR2782646A1 (fr) * 1998-09-02 2000-03-03 Smiths Industries Plc Appareil respiratoire comportant un ensemble indicateur
US6378522B1 (en) 1998-09-02 2002-04-30 Smiths Industries Public Limited Respiration assemblies and indicators
DE10025202A1 (de) * 2000-05-20 2001-11-29 Messer Austria Gmbh Gumpoldski Gasdosiergerät mit Katheter
WO2012030232A1 (fr) * 2010-09-03 2012-03-08 Fisher & Paykel Healthcare Limited Indicateur de respiration
US10149953B2 (en) 2010-09-03 2018-12-11 Fisher & Paykel Healthcare Limited Breath indicator
EP2611486A4 (fr) * 2010-09-03 2015-07-15 Fisher & Paykel Healthcare Ltd Indicateur de respiration
AU2011296642B2 (en) * 2010-09-03 2016-06-23 Fisher & Paykel Healthcare Limited Breath indicator
AU2011296642C1 (en) * 2010-09-03 2016-10-13 Fisher & Paykel Healthcare Limited Breath indicator
US11654254B2 (en) 2010-09-03 2023-05-23 Fisher & Paykel Healthcare Limited Breath indicator
EP3241584A1 (fr) * 2010-09-03 2017-11-08 Fisher&Paykel Healthcare Limited Indicateur d'haleine
AU2020201637B2 (en) * 2010-09-03 2022-10-13 Fisher & Paykel Healthcare Limited Breath indicator
EP3777940A1 (fr) * 2010-09-03 2021-02-17 Fisher & Paykel Healthcare Limited Indicateur de respiration
AU2018203347B2 (en) * 2010-09-03 2019-12-05 Fisher & Paykel Healthcare Limited Breath indicator
WO2012046087A1 (fr) * 2010-10-05 2012-04-12 Symeon Grigoriou Tube endotrachéal comportant un indicateur de ph
US10175254B2 (en) 2013-07-16 2019-01-08 Palo Alto Health Sciences, Inc. Methods and systems for quantitative colorimetric capnometry
US11538569B2 (en) 2013-07-16 2022-12-27 Freespira. Inc. Methods and systems for quantitative colorimetric capnometry
FR3034870A1 (fr) * 2015-04-13 2016-10-14 Commissariat Energie Atomique Capteur chimique de type optode, son procede de preparation et ses utilisations
WO2020109915A1 (fr) 2018-11-27 2020-06-04 Fisher & Paykel Healthcare Limited Indicateur d'haleine
EP3886698A4 (fr) * 2018-11-27 2022-08-10 Fisher & Paykel Healthcare Limited Indicateur d'haleine

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