WO1987000920A1 - Fiber optic probe for quantification of colorimetric reactions - Google Patents
Fiber optic probe for quantification of colorimetric reactions Download PDFInfo
- Publication number
- WO1987000920A1 WO1987000920A1 PCT/US1986/001579 US8601579W WO8700920A1 WO 1987000920 A1 WO1987000920 A1 WO 1987000920A1 US 8601579 W US8601579 W US 8601579W WO 8700920 A1 WO8700920 A1 WO 8700920A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- optical
- optical fiber
- probe
- tip
- sample chamber
- Prior art date
Links
- 239000000523 sample Substances 0.000 title claims abstract description 82
- 239000000835 fiber Substances 0.000 title claims abstract description 26
- 238000006243 chemical reaction Methods 0.000 title 1
- 238000011002 quantification Methods 0.000 title 1
- 239000013307 optical fiber Substances 0.000 claims abstract description 88
- 230000003287 optical effect Effects 0.000 claims abstract description 47
- 239000000126 substance Substances 0.000 claims abstract description 36
- 238000005259 measurement Methods 0.000 claims abstract description 16
- 239000011248 coating agent Substances 0.000 claims description 23
- 238000000576 coating method Methods 0.000 claims description 23
- 239000012528 membrane Substances 0.000 claims description 18
- 230000001681 protective effect Effects 0.000 claims description 15
- 238000005452 bending Methods 0.000 claims description 14
- 239000002245 particle Substances 0.000 claims description 10
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 9
- 239000011521 glass Substances 0.000 claims description 8
- 239000004005 microsphere Substances 0.000 claims description 7
- 239000002002 slurry Substances 0.000 claims description 6
- 239000007787 solid Substances 0.000 claims description 5
- 230000005540 biological transmission Effects 0.000 claims description 4
- 239000007788 liquid Substances 0.000 claims description 4
- 239000012634 fragment Substances 0.000 claims description 3
- 210000004204 blood vessel Anatomy 0.000 claims 1
- 238000003780 insertion Methods 0.000 abstract description 4
- 230000037431 insertion Effects 0.000 abstract description 4
- 239000003086 colorant Substances 0.000 abstract description 2
- 239000000975 dye Substances 0.000 description 10
- 239000000463 material Substances 0.000 description 5
- 229920002301 cellulose acetate Polymers 0.000 description 4
- YMWUJEATGCHHMB-UHFFFAOYSA-N Dichloromethane Chemical compound ClCCl YMWUJEATGCHHMB-UHFFFAOYSA-N 0.000 description 3
- 230000008901 benefit Effects 0.000 description 3
- 230000008859 change Effects 0.000 description 3
- 238000010276 construction Methods 0.000 description 3
- 239000012530 fluid Substances 0.000 description 3
- CSCPPACGZOOCGX-UHFFFAOYSA-N Acetone Chemical compound CC(C)=O CSCPPACGZOOCGX-UHFFFAOYSA-N 0.000 description 2
- 239000004809 Teflon Substances 0.000 description 2
- 229920006362 Teflon® Polymers 0.000 description 2
- 239000000443 aerosol Substances 0.000 description 2
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 2
- 239000008280 blood Substances 0.000 description 2
- 210000004369 blood Anatomy 0.000 description 2
- 238000005520 cutting process Methods 0.000 description 2
- JHIVVAPYMSGYDF-UHFFFAOYSA-N cyclohexanone Chemical compound O=C1CCCCC1 JHIVVAPYMSGYDF-UHFFFAOYSA-N 0.000 description 2
- 235000013372 meat Nutrition 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 239000001301 oxygen Substances 0.000 description 2
- 229910052760 oxygen Inorganic materials 0.000 description 2
- 229920013716 polyethylene resin Polymers 0.000 description 2
- 239000004814 polyurethane Substances 0.000 description 2
- 229920002635 polyurethane Polymers 0.000 description 2
- 239000011148 porous material Substances 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- NSMXQKNUPPXBRG-SECBINFHSA-N (R)-lisofylline Chemical compound O=C1N(CCCC[C@H](O)C)C(=O)N(C)C2=C1N(C)C=N2 NSMXQKNUPPXBRG-SECBINFHSA-N 0.000 description 1
- RZVAJINKPMORJF-UHFFFAOYSA-N Acetaminophen Chemical compound CC(=O)NC1=CC=C(O)C=C1 RZVAJINKPMORJF-UHFFFAOYSA-N 0.000 description 1
- 239000004593 Epoxy Substances 0.000 description 1
- 241000282337 Nasua nasua Species 0.000 description 1
- 241000282320 Panthera leo Species 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 239000002253 acid Substances 0.000 description 1
- 238000000149 argon plasma sintering Methods 0.000 description 1
- JMEAFYJXCJNGCX-UHFFFAOYSA-N butanoic acid;perylene Chemical compound CCCC(O)=O.CCCC(O)=O.C1=CC(C2=CC=CC=3C2=C2C=CC=3)=C3C2=CC=CC3=C1 JMEAFYJXCJNGCX-UHFFFAOYSA-N 0.000 description 1
- 230000005465 channeling Effects 0.000 description 1
- 230000001186 cumulative effect Effects 0.000 description 1
- 235000013399 edible fruits Nutrition 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 239000003822 epoxy resin Substances 0.000 description 1
- 235000013305 food Nutrition 0.000 description 1
- 235000021022 fresh fruits Nutrition 0.000 description 1
- 239000007789 gas Substances 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 238000012623 in vivo measurement Methods 0.000 description 1
- 230000007794 irritation Effects 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- CERQOIWHTDAKMF-UHFFFAOYSA-M methacrylate group Chemical group C(C(=C)C)(=O)[O-] CERQOIWHTDAKMF-UHFFFAOYSA-M 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 239000003960 organic solvent Substances 0.000 description 1
- 238000001139 pH measurement Methods 0.000 description 1
- 239000012466 permeate Substances 0.000 description 1
- 239000007793 ph indicator Substances 0.000 description 1
- KJFMBFZCATUALV-UHFFFAOYSA-N phenolphthalein Chemical compound C1=CC(O)=CC=C1C1(C=2C=CC(O)=CC=2)C2=CC=CC=C2C(=O)O1 KJFMBFZCATUALV-UHFFFAOYSA-N 0.000 description 1
- 229920003229 poly(methyl methacrylate) Polymers 0.000 description 1
- 229920000647 polyepoxide Polymers 0.000 description 1
- 229920000642 polymer Polymers 0.000 description 1
- 239000004926 polymethyl methacrylate Substances 0.000 description 1
- 238000002360 preparation method Methods 0.000 description 1
- 239000011253 protective coating Substances 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 230000035939 shock Effects 0.000 description 1
- 230000011664 signaling Effects 0.000 description 1
- 239000002904 solvent Substances 0.000 description 1
- 238000005406 washing Methods 0.000 description 1
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
- G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
- G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
- G01N21/7703—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator using reagent-clad optical fibres or optical waveguides
Definitions
- This invention relates to a novel apparatus utilizing fiber optics for colorimetric measurement of chemical properties. More particularly, this invention relates to a fiber optic probe which employs a confronting face optical gap measurement configuration while allowing an overall probe diameter sufficiently small to permit the probe to be inserted into living tissue directly or by prior insertion into a 16-gauge or smaller hypodermic needle.
- Colorimetric measurement of chemical properties is well known in the art.
- One simple example is the use of a phenophthalein solution which turns red in the presence of a base while becoming clear in the presence of an acid.
- the use of a colorimetric substance in combination with a fiber optics light source and detector has been taught by many references. Light supplied through a transmitting optical fiber is transmitted through a colorimetric substance mixed with a chemical whose properties are to be measured, and received by a receiving optical fiber which transmits that light to a light detector. A change in color of the colorimetric substance thus changes the light transmissivity of the mixture resulting a different amount of light measured by the light detector.
- the -use of light for the measurement of such quantities as blood pH in vivo is superior to electrical measurement because of the resulting reduced irritation and shock hazard to living tissue.
- the optical fibers provide a means of channeling the light and making a measurement probe of convenient size.
- a first optical fiber is ⁇ connected at one end to a light transmitter and has its opposite end prepared by making a cut at 90° to the axis of the fiber to form a face.
- a second optical fiber is connected to a light detector at one end and has a face prepared on its opposite end in a manner like that of the first optical fiber.
- the faces of the two optical fibers are arranged so as to confront each other, allowing light from the transmitting fiber to be directed through the . chemical to be measured and directly into the i face of the receiving optical fiber.
- the two faces are thus parallel and separated from one another by a distance of typically 0.01 in. so as to form an optical gap.
- the optical fibers may extend away from the optical gap with their respective axes coincident.
- a small and more manageable configuration is made by bending the optical fibers so that they may be arranged parallel to one another at a distance away from the optical gap.
- an optical probe may be constructed in which the body consists of two parallel optical fibers suitably fastened together to produce a relatively small diameter probe body.
- the fundamental lower limit in probe tip size results from the fact that there is a lower limit to the bending radius of the optical fiber.
- the literature of the fiber optics art teaches that-an optical fiber exhibits drarnatical-ly reduced transmissivity when bent with a bending radius near that of its outer diameter.
- a second configuration has been used which allows a smaller probe tip size.
- An example of this configuration is disclosed by Peterson, et al., in U.S. Letters Patent 4,200,110.
- the two optical fibers are arranged parallel to each other along the entire probe length.
- the optical fiber faces are arranged so that they are generally parallel but face the same direction rather tha confronting one another.
- Light reception then depends upon either the light scattering properties of the chemical to be measured, or upon placement of a reflector at the probe tip. While this second configuration does not require the bending of the optical fibers, it does result in a reduce amount light available at the face of the receiving optical fiber.
- a first optical fiber which may be either the transmitting or receiving fiber, is so constructed to have a sharp, 180 bend placed in it near its face so as to form a hook shape.
- the face end of the optical fiber is brought back parallel to and closely spaced from the portion of the fiber on the other side of the bend.
- the bend is referred to as sharp in that the bending radius is smaller than the optical fiber art teaches is possible without unduly reducing the light transmissivity of the ' fiber.
- a sharp bend in an optical fiber is one in which the bending radius is of the same order of magnitude as the diameter of the optical fiber.
- a second optical fiber is laid parallel to the first optical fiber so that its face is parallel to and confronting the face of the first optical fiber.
- a suitably rigid coating material of epoxy resin or the like is applied to the two optical fibers to hold the fibers in their respective positions and give the probe structural strength.
- a sample chamber bored into the protective coating exposes the optical gap and holds the colorimetric substance into which the chemical to be measured is introduced.
- a semipermeable membrane covers the opening of the sample chamber thereby holding in the colorimetric substance while allowing the chemical to be measured to pass into the sample chamber.
- semipermeable as applied to membranes admits of two meanings' in the relevant literature.
- An older meaning relates to membranes' which allow flow of fluid through them in one direction while preventing flow in the opposite directio
- a second meaning of semipermeable as applied to membrane and the meaning used herein relates to membranes which allow flow through them substantially equally well in bo directions of selected fluids while being substantially equally impervious in both directions to other fluids.
- a probe of the type disclosed may be constructed by bending a single optical fiber double in a tight bend and then applying the coati material starting at the tip and moving back along the doubled length of the fiber.
- the coating material has dried to form a rigid coating
- the sample chamber an optical gap are formed by cutting a slit in the probe. - The process of cutting the sample chamber into the tip support coating also results in the severing of the sing optical fiber so as to produce the above recited structu containing two optical fibers.
- the invention incorporates the advantages of the confronting face optical gap of Brumely while achieving the inherently smaller probe tip size of Peterson, et al
- the invention has a further advantage over both the Peterson and Brumley configurations in that the measurement chamber is located on the side of the probe rather than on the tip.
- the tip thus may be made sufficiently strong and small to permit the probe to be inserted directly into living tissue without being first inserted into a hypodermic needle.
- the invention has applications outside the biomedical field in such areas as the food industry.
- Figure 1 is a cross-sectional view of the optical probe showing its details of construction and its connec ⁇ tion to a light source and detector.
- Figure 2 is ' an enlarged cross-sectional view of the probe tip showing the details of the sample chamber.
- Figure 3 illustrates the directional properties of the optical fiber as they relate to the determination of the width of the optical gap.
- a probe body 12 is com ⁇ prised of a first optical fiber 18 and a second optical fi ⁇ ber 16 encapsulated by a protective sheath 14.
- the protec ⁇ tive sheath 14 is preferably a flexible cylindrical tubing approximately 3.5 inches (8.9 cm) in. length made of a mate ⁇ rial such as teflon.
- the teflon tubing is thin walled, having an inner diameter of approcimately 0.02 inch (0.05 mir . and.awall thickness of about 0.002 inch (0.50 mm).
- a tip ' support coating 24 covers the portion of the optical fibers 16 and 18 which protrude about 0.2 inches (5.0mm) from one end of the protective sheath 14, and further extends inside the protective sheath 14.
- a sample chamber 22 opens on the surface of the tip support coating and extends into the interior of the tip support coating 24 for a distance of approximately 0.5 inches (12.7 mm) .
- Figure 3 shows the optical fibers 16 and 18 spaced apart a distance greater than the diameter of the fibers 16 and 18 primarily to better show the details of con ⁇ struction. Also, considerable space is shown between the inner wall of the protective sheath 14 and the optical fibers 16 and 18, again to better show the construction details. In actual implementation, the protective sheath 14 fits tightly over the optical fibers 16 and 18, so as to force the fibers 16 and 18 to touch each other throughout the interior of the protective sheath 14.
- the optical fiber is preferably constructed of polymethyl methacrylate core with an outer covering of transparent polymer of a lower index of refraction than that of the core.
- a typical outer diameter of the fiber used is about 0.01 inches (0.25 mm).
- Fibers of this type, bundled in groups of up to 64 and covered with a polyethylene resin jacket, are sold by Dupont under the registered trademark CROFON.
- a Dupon OE0Q11 optical fiber, not covered by the polyethylene resin jacket, is a suitable fiber for implementation of the present invention.
- the tip support coating 24 is preferably an epoxy material which may be applied as a liquid and allowed to dry to a rigid covering. Although Figure 1 shows the tip support coating 24 to be opaque for clarity, the tip support coating 24 may equally well be transparent or translucent. In addition to providing a rigid protection for the tip and a surrounding medium for the same chamber, the tip support coating helps to anchor the end of the protective sheath 14.
- the distal ends of the optical fibers 16 and 18 are optically connected to a light source 10 and a light detector 12 by means of standard and readily available optical couplers, thus permitting the transmission of light through the optical fibers 16 and 18. It should be 'emphasized that the probe will also function with the light detector 12 connected to the second optical fiber 16 and the light source 10 connected to the first optical fiber 18, allowing the transmission of light in a direction opposite that shown in Figure 1.
- the second optical fiber 16 is arranged parallel and closely spaced from the first optical fiber 18.
- the first optical fiber 18 extends beyond the proximate end of the second optical fiber 16 and traverses a sharp-, 180 bend so that the proximate ends of the optical fibers 16 and 18 confront each other from opposite sides of the sample chamber 22.
- a tip 20 is formed by the sharp, 180 bend.
- the optical fibers 16 and 18 would begin as parts of a single optical fiber doubled and drawn through the protective sheath 14, with the tip support coating 24 applied as a liquid. When the tip supporting 24 has hardened, the sample chamber 22 is cut into the hardened tip supporting 24 with the single optical fiber being thus " severed to form two separate optical fibers 16 and 18 arranged as shown.
- the sharpness of the 180 bend at the tip 20 may be more specifically defined in terms of the bending radius 32 measured from-the center of curvature 33 of the bend to the axis 34 of the first optical fiber 18. So as to effect a small tip size, the bending radius is made less than or equal to the diameter of the first optical - ⁇ - fiber 18.'
- the riber optics art teaches that the trans- r ⁇ issivity of an optical fiber may drop to 60% or less of its straight line transmissivity when bent with a bending radius this small compared to its diameter. Manufacturers of optical- fibers therefore recommend that larger bending radii be used for proper optical fiber operation.
- the successful operation of the ' robe while utilizing a bending radius 32 which is less than or equal to the diameter of the first optical fiber 18 is thus a surprising and non-obvious result in view of the prior art teachings.
- optical fibers 16 and 18 are prepared with faces 28 and 30 respectively.
- the faces 28 and 30 5 are flat and are cut so-as to be generally perpendicular to the axes of optical fibers 16 and 18 respectively and one thus generally parallel to one another.
- the faces 28 and 30 are spaced apart to form an optical gap 23.
- the axis 34, extended beyond face 30 toward face 28, will be 10 seen to be coincident with axis 17.
- a maximum width of the optical gap 23 is determined by two factors. First, as the optical .gap 23 is increased, less light is received at the receiving face
- the face 28 is the transmitting face because the second optical fiber 16 is optically connected to the light source 10.
- the first optical fiber 18 could as well be the fiber optically connected to
- the light source 10 with the light detector 12 being connected to the second optical fiber 16, thus reversing the transmitting and receiving roles of the faces 28 and 30, respectively.
- a second factor affecting the maximum width of the optical gap 23 is the possibility of receiving light at the receiving face 30 from sources other than the transmitting face 28. Referring now to Figure 3, it can be seen that the faces 28 and 30 are directional in their
- Directivity patterns for transmitting and receiving light from the faces of Dupont CROFON optical fibers are shown. Light transmitted from the -transmitting face 28 is primarily confined to a transmitting cone of 20 about the
- the sample chamber 22 is filled with a colorimetric substance 25.
- the colorimetric substance 25 is such that it is permeable to the chemical to be colorimetrically measured.
- the chemical to be colorimetrically measured enters the sample chamber 22 through the semipermeable membrane 26 and permeates the colorimetric substance 25. If the desired property is present in the chemical the colorimetric substance will change color and thus its transmissivity to light will be altered. A change in the intensity of light transmitted from the transmitting face 28 through the sample chamber 22 and received at the receiving face 30 will be detected • by the light detector 12, thus signaling the presence of the property sought to be detected.
- a colorimetric substance 25 is made by introducing a dye into a porous support medium.
- the porous support medium consists of small glass microspheres with a diameter of approximately 10 micrometers mixed with water to form an aqueous slurry. Irregularly shaped particles with maximum dimensions in the range of 1-100 micrometers may be used in place of the microspheres. Polyurethane particles have also been used although better results have been obtained with glass. -l -
- the dye is bound to the particles or microspheres before the water is introduced.
- the addition of water to the particles or microspheres helps to hold the particles or ' microspheres in place when the semipermeable membrane is applied.
- a wide variety of dyes is commercially available in a variety of colors.
- One example of a dye which has been by some researchers used for the colorimetric measurement of oxygen absorption in the blood is perylene dibutyrate, sold as Thermoplast Brilliant Yellow 10G by BASF-Wyandotte Corporation.
- the binding of the dye to the support- medium may be accomplished by washing the glass particles or microspheres with the dye mixed with an organic solvent such as dichloromethane.
- an organic solvent such as dichloromethane.
- a porous support medium may also be implemented using a solid, porous material such as glass or polyurethane filling the sample chamber.
- Dye of a suitable type may be imparted into the interstices of the medium and allowed to adhere to the walls thereof. Experimentation has shown the slurry type medium to be somewhat easier to apply to the sample chamber. -.3-
- the semipermeable membrane 26 is preferably implemented by applying a 2% solution of a cellulose acetate dissolved in a solvent made of 50% acetone and 50% , cyclohexanone. The solution is sprayed on as an aerosol after the aqueous slurry is introduced into the sample chamber 22. The aerosol will dry to form a membrane 26 which will serve to hold in the glass particles of the porous support medium while allowing water to flow through the membrane 25.
Abstract
A fiber optical probe (12) for colorimetric measurement of chemical properties suitable for the insertion into living tissue. A chemical to be colorimetrically measured is introduced into a sample chamber (22) on the side of the probe (12) near the probe tip (20). A colorimetric substance contained in the sample chamber (22) changes colors in response to chemical properties of the chemical to be colorimetrically measured, thereby changing the amount of light transmitted through the sample chamber (22) by the optical fibers (10, 12).
Description
. BACKGROUND OF THE INVENTION
Technical Field
This invention relates to a novel apparatus utilizing fiber optics for colorimetric measurement of chemical properties. More particularly, this invention relates to a fiber optic probe which employs a confronting face optical gap measurement configuration while allowing an overall probe diameter sufficiently small to permit the probe to be inserted into living tissue directly or by prior insertion into a 16-gauge or smaller hypodermic needle.
Background Art
Colorimetric measurement of chemical properties is well known in the art. One simple example is the use of a phenophthalein solution which turns red in the presence of a base while becoming clear in the presence of an acid. The use of a colorimetric substance in combination with a fiber optics light source and detector has been taught by many references. Light supplied through a transmitting optical fiber is transmitted through a colorimetric substance mixed with a chemical whose properties are to be measured, and received by a receiving optical fiber which transmits that light to a light detector. A change in color of the colorimetric substance thus changes the light transmissivity of the mixture resulting a different amount of light measured by the light detector. The -use of light for the measurement of such quantities as blood pH in vivo is superior to electrical measurement because of the resulting reduced irritation and shock hazard to living tissue. The optical fibers provide a means of channeling the light and making a measurement probe of convenient size.
~z-
In prior art configurations, a first optical fiber is ^connected at one end to a light transmitter and has its opposite end prepared by making a cut at 90° to the axis of the fiber to form a face. A second optical fiber is connected to a light detector at one end and has a face prepared on its opposite end in a manner like that of the first optical fiber.
In one common configuration, the faces of the two optical fibers are arranged so as to confront each other, allowing light from the transmitting fiber to be directed through the .chemical to be measured and directly into the i face of the receiving optical fiber. The two faces are thus parallel and separated from one another by a distance of typically 0.01 in. so as to form an optical gap. In the simplest configuration of this type, the optical fibers may extend away from the optical gap with their respective axes coincident. A small and more manageable configuration is made by bending the optical fibers so that they may be arranged parallel to one another at a distance away from the optical gap. Such a configuration has been taught in U. S. Letters Patent 3,123,066 by Brumley.
Using the configuration as taught by Brumley, an optical probe may be constructed in which the body consists of two parallel optical fibers suitably fastened together to produce a relatively small diameter probe body. There has been thought to exist a fundamental lowe limit to probe tip size, since the respective optical fibers must be bent away from the direction of the probe body direction near the tip and then bent back toward eac other to permit the respective faces to closely confront each other at the optical gap. The fundamental lower limit in probe tip size results from the fact that there is a lower limit to the bending radius of the optical
fiber. The literature of the fiber optics art teaches that-an optical fiber exhibits drarnatical-ly reduced transmissivity when bent with a bending radius near that of its outer diameter.
A second configuration has been used which allows a smaller probe tip size. An example of this configuration is disclosed by Peterson, et al., in U.S. Letters Patent 4,200,110. The two optical fibers are arranged parallel to each other along the entire probe length. At the tip, the optical fiber faces are arranged so that they are generally parallel but face the same direction rather tha confronting one another. In such a configuration, light is transmitted into the chemical to be measured, thence reflected back to be received at the face of the receiving optical fiber. Light reception then depends upon either the light scattering properties of the chemical to be measured, or upon placement of a reflector at the probe tip. While this second configuration does not require the bending of the optical fibers, it does result in a reduce amount light available at the face of the receiving optical fiber.
Both configurations have a common disadvantage, in that the measurement chamber is located at the tip of the probe. This limits the sharpness of the probe. Also, there is a greater opportunity for tip breakage if the probe is inserted directly into living tissue. In the prior art, one way of protecting the probe tip has been t insert the probe into a hypodermic needle, and then inser the needle Into living tissue. Placement of shielding material at the probe tip interferes with the introductio of the chemical to be colorimetrically measured into the measurement chamber.
SUMMARY OF THE INVENTION
The present invention provides a confronting face optical gap measurement configuration without the 'attendant large probe tip size disadvantage found in the prior art. In the present invention, a first optical fiber, which may be either the transmitting or receiving fiber, is so constructed to have a sharp, 180 bend placed in it near its face so as to form a hook shape. The face end of the optical fiber is brought back parallel to and closely spaced from the portion of the fiber on the other side of the bend. The bend is referred to as sharp in that the bending radius is smaller than the optical fiber art teaches is possible without unduly reducing the light transmissivity of the 'fiber. More specifically, a sharp bend in an optical fiber is one in which the bending radius is of the same order of magnitude as the diameter of the optical fiber.
A second optical fiber is laid parallel to the first optical fiber so that its face is parallel to and confronting the face of the first optical fiber. A suitably rigid coating material of epoxy resin or the like, is applied to the two optical fibers to hold the fibers in their respective positions and give the probe structural strength. A sample chamber bored into the protective coating exposes the optical gap and holds the colorimetric substance into which the chemical to be measured is introduced. A semipermeable membrane covers the opening of the sample chamber thereby holding in the colorimetric substance while allowing the chemical to be measured to pass into the sample chamber.
It should be noted that the term semipermeable as applied to membranes admits of two meanings' in the relevant literature. An older meaning relates to
membranes' which allow flow of fluid through them in one direction while preventing flow in the opposite directio A second meaning of semipermeable as applied to membrane and the meaning used herein, relates to membranes which allow flow through them substantially equally well in bo directions of selected fluids while being substantially equally impervious in both directions to other fluids.
The above description recites the use of two optic fibers, one of which has a tight bend placed in it befor probe assembly. In practice, a probe of the type disclosed may be constructed by bending a single optical fiber double in a tight bend and then applying the coati material starting at the tip and moving back along the doubled length of the fiber. When the coating material has dried to form a rigid coating, the sample chamber an optical gap are formed by cutting a slit in the probe. - The process of cutting the sample chamber into the tip support coating also results in the severing of the sing optical fiber so as to produce the above recited structu containing two optical fibers.
The invention incorporates the advantages of the confronting face optical gap of Brumely while achieving the inherently smaller probe tip size of Peterson, et al The invention has a further advantage over both the Peterson and Brumley configurations in that the measurement chamber is located on the side of the probe rather than on the tip. The tip thus may be made sufficiently strong and small to permit the probe to be inserted directly into living tissue without being first inserted into a hypodermic needle.
The invention has applications outside the biomedical field in such areas as the food industry. Fo example, the ruggedness and small size of the probe, tip
allow insertion into fresh fruit or meat to measure chem- ical properties therein. Only minimal deformation of the fruit or meat will result from the insertion due to the tip's small size.
BRIEF DESCRIPTION OF THE DRAWINGS
The advantages and features of the invention may' be more fully understood from the following description read in conjunction with the accompanying drawings, wherein:
Figure 1 is a cross-sectional view of the optical probe showing its details of construction and its connec¬ tion to a light source and detector.
Figure 2 is' an enlarged cross-sectional view of the probe tip showing the details of the sample chamber.
Figure 3 illustrates the directional properties of the optical fiber as they relate to the determination of the width of the optical gap.
DESCRIPTION OF THE PREFERRED EMBODIMENT Referring now to Figure 1, a cross-sectional viewof the optical probe may be seen. A probe body 12 is com¬ prised of a first optical fiber 18 and a second optical fi¬ ber 16 encapsulated by a protective sheath 14. The protec¬ tive sheath 14 is preferably a flexible cylindrical tubing approximately 3.5 inches (8.9 cm) in. length made of a mate¬ rial such as teflon. The teflon tubing is thin walled, having an inner diameter of approcimately 0.02 inch (0.05 mir. and.awall thickness of about 0.002 inch (0.50 mm). A tip' support coating 24 covers the portion of the optical fibers 16 and 18 which protrude about 0.2 inches (5.0mm) from one end of the protective sheath 14, and further extends
inside the protective sheath 14. A sample chamber 22 opens on the surface of the tip support coating and extends into the interior of the tip support coating 24 for a distance of approximately 0.5 inches (12.7 mm) .
Figure 3 shows the optical fibers 16 and 18 spaced apart a distance greater than the diameter of the fibers 16 and 18 primarily to better show the details of con¬ struction. Also, considerable space is shown between the inner wall of the protective sheath 14 and the optical fibers 16 and 18, again to better show the construction details. In actual implementation, the protective sheath 14 fits tightly over the optical fibers 16 and 18, so as to force the fibers 16 and 18 to touch each other throughout the interior of the protective sheath 14.
The optical fiber is preferably constructed of polymethyl methacrylate core with an outer covering of transparent polymer of a lower index of refraction than that of the core. A typical outer diameter of the fiber used is about 0.01 inches (0.25 mm). Fibers of this type, bundled in groups of up to 64 and covered with a polyethylene resin jacket, are sold by Dupont under the registered trademark CROFON. A Dupon OE0Q11 optical fiber, not covered by the polyethylene resin jacket, is a suitable fiber for implementation of the present invention.
The tip support coating 24 is preferably an epoxy material which may be applied as a liquid and allowed to dry to a rigid covering. Although Figure 1 shows the tip support coating 24 to be opaque for clarity, the tip support coating 24 may equally well be transparent or translucent. In addition to providing a rigid protection for the tip and a surrounding medium for the same chamber, the tip support coating helps to anchor the end of the protective sheath 14.
The distal ends of the optical fibers 16 and 18 are optically connected to a light source 10 and a light detector 12 by means of standard and readily available optical couplers, thus permitting the transmission of light through the optical fibers 16 and 18. It should be 'emphasized that the probe will also function with the light detector 12 connected to the second optical fiber 16 and the light source 10 connected to the first optical fiber 18, allowing the transmission of light in a direction opposite that shown in Figure 1.
It can be seen that the second optical fiber 16 is arranged parallel and closely spaced from the first optical fiber 18. The first optical fiber 18 extends beyond the proximate end of the second optical fiber 16 and traverses a sharp-, 180 bend so that the proximate ends of the optical fibers 16 and 18 confront each other from opposite sides of the sample chamber 22. A tip 20 is formed by the sharp, 180 bend. In practical construction, the optical fibers 16 and 18 would begin as parts of a single optical fiber doubled and drawn through the protective sheath 14, with the tip support coating 24 applied as a liquid. When the tip supporting 24 has hardened, the sample chamber 22 is cut into the hardened tip supporting 24 with the single optical fiber being thus " severed to form two separate optical fibers 16 and 18 arranged as shown.
Referring now to Figure 2, a more detailed view of the optical probe near the tip 20 and sample chamber 22 may be seen. The sharpness of the 180 bend at the tip 20 may be more specifically defined in terms of the bending radius 32 measured from-the center of curvature 33 of the bend to the axis 34 of the first optical fiber 18. So as to effect a small tip size, the bending radius is made less than or equal to the diameter of the first optical
- ^ - fiber 18.' The riber optics art teaches that the trans- rπissivity of an optical fiber may drop to 60% or less of its straight line transmissivity when bent with a bending radius this small compared to its diameter. Manufacturers of optical- fibers therefore recommend that larger bending radii be used for proper optical fiber operation. The successful operation of the' robe while utilizing a bending radius 32 which is less than or equal to the diameter of the first optical fiber 18 is thus a surprising and non-obvious result in view of the prior art teachings.
Proper functioning of the probe with such a small bending radius 32 in contradiction to the accepted understanding in the optical fiber art appears to be based on two factors. First, many applications require optical fiber runs of tens to hundreds of feet in length in which many bends may be required. In such an application, the cumulative reductions in transmissivity caused by long fiber lengths and multiple bends require limitation of losses due to any one bend. The present invention requires a fiber length of the order of 3 feet (2.34 mm) or less and only one high loss bend. Thus, the high transmis¬ sivity loss occasioned by the bend at the tip 20 is not fatal to probe operation.
Secondly, many fiber optics applications involve the transmission of complex waveforms such as that of speech. Small radius bends such as that used in the present invention will cause severe distortion of such complex waveforms. In the present invention, only the amplitude of the light transmitted is measured, so that waveform distortion and resulting unintelligibility of the transmitted light signal is not a factor in probe operation.
Further referring to Figure 2, details of the sample chamber 22 and the surrounding structure may be seen. The proximate ends of optical fibers 16 and 18 are prepared with faces 28 and 30 respectively. The faces 28 and 30 5 .are flat and are cut so-as to be generally perpendicular to the axes of optical fibers 16 and 18 respectively and one thus generally parallel to one another. The faces 28 and 30 are spaced apart to form an optical gap 23. The axis 34, extended beyond face 30 toward face 28, will be 10 seen to be coincident with axis 17.
A maximum width of the optical gap 23 is determined by two factors. First, as the optical .gap 23 is increased, less light is received at the receiving face
15 from the transmitting face. Note that in Figure 2 the face 28 is the transmitting face because the second optical fiber 16 is optically connected to the light source 10. As previously disclosed, the first optical fiber 18 could as well be the fiber optically connected to
20 the light source 10, with the light detector 12 being connected to the second optical fiber 16, thus reversing the transmitting and receiving roles of the faces 28 and 30, respectively.
25. A second factor affecting the maximum width of the optical gap 23 is the possibility of receiving light at the receiving face 30 from sources other than the transmitting face 28. Referring now to Figure 3, it can be seen that the faces 28 and 30 are directional in their
30 respective transmitting and receiving functions.
Directivity patterns for transmitting and receiving light from the faces of Dupont CROFON optical fibers are shown. Light transmitted from the -transmitting face 28 is primarily confined to a transmitting cone of 20 about the
35 axis 17 of the second optical fiber 16. The receiving face 30 takes in light which is primarily confined to a
- reception cone of 60 about the axis 34 of the first optical fiber 18. If faces 28 and 30 are separated by a distance X greater than d/2 tan 30 = 0.868d, where d is the diameter of the optical fibers, light may be received from ambient sources other than the transmitting face 28, thereby influencing the accuracy of the measurement. Experimentation has shown that examples of the invention having an optical gap 23 of width equal to 1.5 times the diameter of the fibers 16 and 18 are workable but inefficient.
Referring again to Figure 2, it is seen that the sample chamber 22 is filled with a colorimetric substance 25. The colorimetric substance 25 is such that it is permeable to the chemical to be colorimetrically measured. During the measurement process, the chemical to be colorimetrically measured enters the sample chamber 22 through the semipermeable membrane 26 and permeates the colorimetric substance 25. If the desired property is present in the chemical the colorimetric substance will change color and thus its transmissivity to light will be altered. A change in the intensity of light transmitted from the transmitting face 28 through the sample chamber 22 and received at the receiving face 30 will be detected • by the light detector 12, thus signaling the presence of the property sought to be detected.
A colorimetric substance 25 is made by introducing a dye into a porous support medium. ' One practical embodiment of the porous support medium consists of small glass microspheres with a diameter of approximately 10 micrometers mixed with water to form an aqueous slurry. Irregularly shaped particles with maximum dimensions in the range of 1-100 micrometers may be used in place of the microspheres. Polyurethane particles have also been used although better results have been obtained with glass.
-l -
The dye is bound to the particles or microspheres before the water is introduced. The addition of water to the particles or microspheres helps to hold the particles or 'microspheres in place when the semipermeable membrane is applied.
A wide variety of dyes is commercially available in a variety of colors. One example of a dye which has been by some researchers used for the colorimetric measurement of oxygen absorption in the blood is perylene dibutyrate, sold as Thermoplast Brilliant Yellow 10G by BASF-Wyandotte Corporation. The binding of the dye to the support- medium may be accomplished by washing the glass particles or microspheres with the dye mixed with an organic solvent such as dichloromethane. A more detailed description of dye selection and the preparation of the porous support medium and dye is presented in the paper entitled "Fiber- Optic Probe for In Vivo Measurement of Oxygen Partial Pressure" by Peterson, Fitzgerald and Buckhold in Analytical Chemistry, Vol. 56, No. 1, January, 1984.
Harper, in his article entitled "Reusable Glass-Bound pH Indicators" published in Analytical Chemistry, Vol. 47, No. 2, February, 1975, has taught the use of an • immobilized subtheilein indicator dye bound to glass fragments for use in pH measurements.
A porous support medium may also be implemented using a solid, porous material such as glass or polyurethane filling the sample chamber. Dye of a suitable type may be imparted into the interstices of the medium and allowed to adhere to the walls thereof. Experimentation has shown the slurry type medium to be somewhat easier to apply to the sample chamber.
-.3-
' The semipermeable membrane 26 is preferably implemented by applying a 2% solution of a cellulose acetate dissolved in a solvent made of 50% acetone and 50% , cyclohexanone. The solution is sprayed on as an aerosol after the aqueous slurry is introduced into the sample chamber 22. The aerosol will dry to form a membrane 26 which will serve to hold in the glass particles of the porous support medium while allowing water to flow through the membrane 25.
Increasing the concentration of the cellulose acetate in the solution will result in a smaller pore size in the membrane 26. Extensive literature available on the manufacture of cellulose acetate membranes" teaches that concentration of cellulose acetate higher than 2% may be used to produce a membrane permeable to gasses while nonpermeable to water. Such a membrane 26 would be used to hold in the water in the slurry so that a gas to be colorimetrically measured would be dissolved in the water.
Claims
1. An optical probe for colorimetric measurement, including an optical fiber, the ends of said optical fiber being prepared to accept the mounting of optical couplers to enable the transmission of light through said optical fiber, said optical fiber being doubled and having a sharp, 180° bend at a point along its length so as to-form a tip, said optical fiber haing a small slice extracted from it at a point along its length spaced away from the tip so as to form an optical gap, a tip support coating, said tip sup¬ port coating covering thetip and further extending back along and covering the doubled length of said optical fiber for a distance beyond the optical gap, said tip support coating having a sample chamber which opens on the surface of said tip support coating and which extends into the in¬ terior of said tip support coating so as to expose the faces of said optical fiber at the optical gap, a colorimetric substance, said colorimetric substance filling the sample chamber, said colorimetric substance being permeable to a chemical of which properties are to be colorimetrically measured, and a semipermeable membrane,, said semipermeable membrane being applied to the surface of said tip support coating so as to cover the opening of the sample chamber.
2. The optical probe of claim 1, wherein the outer diameter of said optical probe is small enough to permit said optical probe to be inserted into a 16 gauge hypodermic needle.
3. The optical probe of claim 1, wherein the outer diameter of said optical probe is small enouαh to permit said optical probe to be inserted into a blood vessel.
4. The optical probe of claim-1, 2 or 3, wherein said colorimetric substance- is comprised of a porous sup¬ port medium with a dye bound thereto.
5. The optical probe of claim 4, wherein said por¬ ous support medium is comprised of a solid porous material- with the dye bound to the interstices thereof.
6. The optical probe of claim 4, wherein said porous support medium is comprised of solid particles mixed with a liquid to form a slurry,
7. The optical probe of claim 6, wherein said solid particles are made of glass.
8. The optical probe of claim 6, wherein said solid particles are microspheres.
9. The optical probe of claim 6, wherein said liquid is water.
10. An optical probe for colorimetric measurement, including a first optical fiber having a distal end pre¬ pared to accept an optical coupler and a proximate end having a face, said first optical fiber having a 180° bend near its proximate end to form a tip, with bending radius being less than or equal to the diameter of said first op¬ tical fiber, a second optical fiber having a distal end prepared to accept an optical coupler and a proximate end having a face, said second optical fiber being placed closely to and running parallel to said first optical fiber so that the proximate end face of said first optical fiber confronts the proximate end face of said second optical fiber to form an optical gap, a flexible protective sheath surrounding said optical fibers, the respective proximate ends of said optical fibers protruding from the proximate end of said flexible protective sheath so as to leave the tip and the optical gap exposed, the distal ends of said optical fibers protruding from the distal end of said flex¬ ible protective sheath, a rigid tip support coating cover¬ ing that part of the proximate ends of said optical fibers exposed by said protective sheath and further extending inside and filling the interior of said protective sheath near the proximate end of said protective sheath, said tip support coating having a sample chamber opening on the sur¬ face of said tip support coating and extending inward into said tip support coating and the optical gap so as to ex¬ pose the proximate end faces of said optical fibers, a colorimetric substance filling said sample chamber, said colorimetric substance comprised of glass fragments with - 16 - a dye bound' thereto , the fragments being mixed with water to form a slurry, and a semipermeable membrane applied to the surface of said tip support coating so as to cover the opening of the sample chamber, said semipermeable. embrane extending back along said optical probe so as to cover a portion of said protective sheath, said semipermeable membrane being chosen so as to allow the flow of a selected chemical to be colorimetrically measured while prohibiting the flow of other chemicals.
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AT86905053T ATE48701T1 (en) | 1985-08-06 | 1986-07-31 | FIBER OPTIC PROBE DEVICE FOR MEASUREMENT OF COLOR RESPONSE. |
JP61504393A JPH0697206B2 (en) | 1985-08-06 | 1986-07-31 | Fiber optic probe for quantification of colorimetric reactions |
DE8686905053T DE3667541D1 (en) | 1985-08-06 | 1986-07-31 | FIBER OPTICAL PROBE DEVICE FOR MEASURING COLOR REACTIONS. |
SU874202483A RU1830141C (en) | 1985-08-06 | 1987-04-03 | Optical-fibre probe for colorimetric measurements |
KR870700296A KR880700259A (en) | 1985-08-06 | 1987-04-06 | Optical probe |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US763,019 | 1985-08-06 | ||
US06/763,019 US4682895A (en) | 1985-08-06 | 1985-08-06 | Fiber optic probe for quantification of colorimetric reactions |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1987000920A1 true WO1987000920A1 (en) | 1987-02-12 |
Family
ID=25066670
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1986/001579 WO1987000920A1 (en) | 1985-08-06 | 1986-07-31 | Fiber optic probe for quantification of colorimetric reactions |
Country Status (9)
Country | Link |
---|---|
US (1) | US4682895A (en) |
EP (1) | EP0232369B1 (en) |
JP (1) | JPH0697206B2 (en) |
KR (1) | KR880700259A (en) |
CN (1) | CN1009955B (en) |
CA (1) | CA1292665C (en) |
DE (1) | DE3667541D1 (en) |
RU (1) | RU1830141C (en) |
WO (1) | WO1987000920A1 (en) |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0234928A2 (en) * | 1986-02-27 | 1987-09-02 | Eli Lilly And Company | Optical fiber apparatus |
EP0352610A2 (en) * | 1988-07-25 | 1990-01-31 | Abbott Laboratories | Fiber-optic physiological probes |
WO1991018306A2 (en) * | 1990-05-22 | 1991-11-28 | Optex Biomedical, Inc. | Optical probe |
EP0579257A1 (en) * | 1992-07-17 | 1994-01-19 | ULTRAKUST electronic GmbH | Device for determining optical spectral shifts caused by physical or chemical effects |
WO1994010554A1 (en) * | 1992-10-23 | 1994-05-11 | Optex Biomedical, Inc. | Method of making an optical fibre sensor probe |
WO1994010553A1 (en) * | 1992-10-23 | 1994-05-11 | Optex Biomedical, Inc. | Fibre-optic probe for the measurement of fluid parameters |
GB2283567A (en) * | 1993-10-29 | 1995-05-10 | Univ Brunel | Fibre optic sensor device |
WO2008098087A3 (en) * | 2007-02-06 | 2008-11-27 | Glumetrics Inc | Optical systems and methods for rationmetric measurement of blood glucose concentration |
US7751863B2 (en) | 2007-02-06 | 2010-07-06 | Glumetrics, Inc. | Optical determination of ph and glucose |
US8979790B2 (en) | 2007-11-21 | 2015-03-17 | Medtronic Minimed, Inc. | Use of an equilibrium sensor to monitor glucose concentration |
Families Citing this family (162)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE3001669A1 (en) * | 1980-01-18 | 1981-08-06 | Max-Planck-Gesellschaft zur Förderung der Wissenschaften e.V., 3400 Göttingen | ARRANGEMENT FOR OPTICAL MEASUREMENT OF PHYSICAL SIZES AND SUBSTANCE CONCENTRATIONS |
US4929561A (en) * | 1985-08-08 | 1990-05-29 | Regents Of The University Of California | Absorption-emission optrode and methods of use thereof |
US5006314A (en) * | 1986-04-18 | 1991-04-09 | Minnesota Mining And Manufacturing Company | Sensor and method for sensing the concentration of a component in a medium |
US4919891A (en) * | 1986-04-18 | 1990-04-24 | Minnesota Mining And Manufacturing Company | Sensor with overcoating and process for making same |
US4981779A (en) * | 1986-06-26 | 1991-01-01 | Becton, Dickinson And Company | Apparatus for monitoring glucose |
US5001054A (en) * | 1986-06-26 | 1991-03-19 | Becton, Dickinson And Company | Method for monitoring glucose |
US4800886A (en) * | 1986-07-14 | 1989-01-31 | C. R. Bard, Inc. | Sensor for measuring the concentration of a gaseous component in a fluid by absorption |
US4820490A (en) * | 1986-09-11 | 1989-04-11 | Miles Inc. | Device and method for chemical analysis of fluids with a reagent coated light source |
US5075127A (en) * | 1986-10-10 | 1991-12-24 | Minnesota Mining And Manufacturing Company | Sensor with overcoating and process for making same |
US4886338A (en) * | 1986-10-10 | 1989-12-12 | Minnesota Mining And Manufacturing Company | Optical fiber event sensor |
US5120510A (en) * | 1986-10-10 | 1992-06-09 | Minnesota Mining And Manufacturing Company | Sensor and method for sensing the concentration of a component in a medium |
US5151598A (en) * | 1987-03-17 | 1992-09-29 | Neoprobe Corporation | Detector and localizer for low energy radiation emissions |
US5070878A (en) * | 1988-11-14 | 1991-12-10 | Neoprobe Corporation | Detector and localizer for low energy radiation emissions |
FR2613074B1 (en) * | 1987-03-27 | 1990-06-08 | Commissariat Energie Atomique | ACTIVE CHEMICAL SENSOR WITH OPTICAL FIBERS |
US4810051A (en) * | 1987-03-27 | 1989-03-07 | Thomas & Betts Corporation | Optical fiber modulator |
US4849340A (en) * | 1987-04-03 | 1989-07-18 | Cardiovascular Diagnostics, Inc. | Reaction system element and method for performing prothrombin time assay |
US4842783A (en) * | 1987-09-03 | 1989-06-27 | Cordis Corporation | Method of producing fiber optic chemical sensors incorporating photocrosslinked polymer gels |
US5037615A (en) * | 1987-10-30 | 1991-08-06 | Cordis Corporation | Tethered pair fluorescence energy transfer indicators, chemical sensors, and method of making such sensors |
US4824206A (en) * | 1987-11-25 | 1989-04-25 | St&E, Inc. | Modular fiber optic chemical sensor |
US4991590A (en) * | 1989-01-30 | 1991-02-12 | Martin Goffman Associates | Fiber optic intravascular blood pressure transducer |
US4892383A (en) * | 1989-02-17 | 1990-01-09 | Fiberchem Inc. | Reservoir fiber optic chemical sensors |
US5047208A (en) * | 1989-02-23 | 1991-09-10 | Medtronic, Inc. | Blood gas monitoring sensors |
US5402241A (en) * | 1989-03-30 | 1995-03-28 | The Foxboro Company | Optical probe for fluid light transmission properties |
US5166073A (en) * | 1989-05-05 | 1992-11-24 | The Dow Chemical Company | Miniaturized sensor for ionizing radiation |
US5094819A (en) * | 1989-06-16 | 1992-03-10 | Washington Research Foundation | Fluorescence-based optical sensor and method for detection of lipid-soluble analytes |
US5176881A (en) * | 1989-08-11 | 1993-01-05 | The University Of Tennessee Research Corporation | Fiber optic-based regenerable biosensor |
US5056520A (en) * | 1989-10-11 | 1991-10-15 | Medex, Inc. | Probe for blood gas sensing |
US5132057A (en) * | 1989-10-11 | 1992-07-21 | Medex, Inc. | Method of making an optical fiber probe |
US5063178A (en) * | 1990-03-19 | 1991-11-05 | Medex, Inc. | Freeze-dried blood gas sensor |
US5109442A (en) * | 1990-03-28 | 1992-04-28 | Fiberchem Inc. | Waterproof optical fiber chemical sensor and method of making same |
US5059790A (en) * | 1990-03-30 | 1991-10-22 | Fiberchem, Inc. | Reservoir fiber optic chemical sensors |
US5271073A (en) * | 1990-08-10 | 1993-12-14 | Puritan-Bennett Corporation | Optical fiber sensor and method of manufacture |
US5166990A (en) * | 1990-08-10 | 1992-11-24 | Puritan-Bennett Corporation | Multiple optical fiber event sensor and method of manufacture |
US5054882A (en) * | 1990-08-10 | 1991-10-08 | Puritan-Bennett Corporation | Multiple optical fiber event sensor and method of manufacture |
US5152287A (en) * | 1990-08-15 | 1992-10-06 | Cordis Corporation | Cross-linked fluorinated polymers for use in gas sensors |
US5212099A (en) * | 1991-01-18 | 1993-05-18 | Eastman Kodak Company | Method and apparatus for optically measuring concentration of an analyte |
US5187366A (en) * | 1991-06-25 | 1993-02-16 | Joram Hopenfeld | Sensors for detecting leaks |
US5200615A (en) * | 1991-06-25 | 1993-04-06 | Joram Hopenfeld | Method and apparatus for detecting the presence of fluids |
US5650331A (en) * | 1991-10-03 | 1997-07-22 | The United States Of America As Represented By The United States Department Of Energy | Optical high acidity sensor |
US5271398A (en) * | 1991-10-09 | 1993-12-21 | Optex Biomedical, Inc. | Intra-vessel measurement of blood parameters |
US5342190A (en) * | 1992-07-22 | 1994-08-30 | Optex Biomedical, Inc. | Apparatus for emplacing viscous material in a cavity |
US6335203B1 (en) * | 1994-09-08 | 2002-01-01 | Lifescan, Inc. | Optically readable strip for analyte detection having on-strip orientation index |
US5526120A (en) * | 1994-09-08 | 1996-06-11 | Lifescan, Inc. | Test strip with an asymmetrical end insuring correct insertion for measuring |
MX9701792A (en) * | 1994-09-08 | 1997-06-28 | Johnson & Johnson | Optically readable strip for analyte detection having on-strip standard. |
US5515170A (en) * | 1994-09-08 | 1996-05-07 | Lifescan, Inc. | Analyte detection device having a serpentine passageway for indicator strips |
US5563031A (en) * | 1994-09-08 | 1996-10-08 | Lifescan, Inc. | Highly stable oxidative coupling dye for spectrophotometric determination of analytes |
US5652810A (en) * | 1996-05-09 | 1997-07-29 | The United States Of America As Represented By The Secretary Of The Air Force | Fiber optic sensor for site monitoring |
US5763277A (en) * | 1996-06-10 | 1998-06-09 | Transgenomic Incorporated | Fiber optic axial view fluorescence detector and method of use |
US6008055A (en) * | 1998-06-30 | 1999-12-28 | Transgenomic, Inc. | Modular component fiber optic fluorescence detector system, and method of use |
US6815211B1 (en) | 1998-08-04 | 2004-11-09 | Ntc Technology | Oxygen monitoring methods and apparatus (I) |
US20070225612A1 (en) * | 1996-07-15 | 2007-09-27 | Mace Leslie E | Metabolic measurements system including a multiple function airway adapter |
US7335164B2 (en) | 1996-07-15 | 2008-02-26 | Ntc Technology, Inc. | Multiple function airway adapter |
US6325978B1 (en) | 1998-08-04 | 2001-12-04 | Ntc Technology Inc. | Oxygen monitoring and apparatus |
US5696592A (en) * | 1996-12-11 | 1997-12-09 | Kuan; Ching Fu | Immersible apparatus for measuring light penetrability of liquids |
US6144790A (en) * | 1997-02-07 | 2000-11-07 | Bledin; Anthony G | Contact fiber optic impact sensor |
US6023540A (en) | 1997-03-14 | 2000-02-08 | Trustees Of Tufts College | Fiber optic sensor with encoded microspheres |
US6327410B1 (en) * | 1997-03-14 | 2001-12-04 | The Trustees Of Tufts College | Target analyte sensors utilizing Microspheres |
US7622294B2 (en) * | 1997-03-14 | 2009-11-24 | Trustees Of Tufts College | Methods for detecting target analytes and enzymatic reactions |
US20030027126A1 (en) * | 1997-03-14 | 2003-02-06 | Walt David R. | Methods for detecting target analytes and enzymatic reactions |
US6406845B1 (en) | 1997-05-05 | 2002-06-18 | Trustees Of Tuft College | Fiber optic biosensor for selectively detecting oligonucleotide species in a mixed fluid sample |
US7115884B1 (en) | 1997-10-06 | 2006-10-03 | Trustees Of Tufts College | Self-encoding fiber optic sensor |
US7348181B2 (en) | 1997-10-06 | 2008-03-25 | Trustees Of Tufts College | Self-encoding sensor with microspheres |
US6210910B1 (en) | 1998-03-02 | 2001-04-03 | Trustees Of Tufts College | Optical fiber biosensor array comprising cell populations confined to microcavities |
US6299583B1 (en) | 1998-03-17 | 2001-10-09 | Cardiox Corporation | Monitoring total circulating blood volume and cardiac output |
US6922576B2 (en) * | 1998-06-19 | 2005-07-26 | Becton, Dickinson And Company | Micro optical sensor device |
AU754952B2 (en) | 1998-06-24 | 2002-11-28 | Illumina, Inc. | Decoding of array sensors with microspheres |
US7612020B2 (en) | 1998-12-28 | 2009-11-03 | Illumina, Inc. | Composite arrays utilizing microspheres with a hybridization chamber |
US6429027B1 (en) | 1998-12-28 | 2002-08-06 | Illumina, Inc. | Composite arrays utilizing microspheres |
US6244214B1 (en) | 1999-01-06 | 2001-06-12 | Embrex, Inc. | Concurrent in ovo injection and detection method and apparatus |
US20060275782A1 (en) | 1999-04-20 | 2006-12-07 | Illumina, Inc. | Detection of nucleic acid reactions on bead arrays |
US20030215821A1 (en) * | 1999-04-20 | 2003-11-20 | Kevin Gunderson | Detection of nucleic acid reactions on bead arrays |
US6355431B1 (en) | 1999-04-20 | 2002-03-12 | Illumina, Inc. | Detection of nucleic acid amplification reactions using bead arrays |
US6620584B1 (en) | 1999-05-20 | 2003-09-16 | Illumina | Combinatorial decoding of random nucleic acid arrays |
US6544732B1 (en) * | 1999-05-20 | 2003-04-08 | Illumina, Inc. | Encoding and decoding of array sensors utilizing nanocrystals |
US8080380B2 (en) * | 1999-05-21 | 2011-12-20 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
US8481268B2 (en) | 1999-05-21 | 2013-07-09 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
WO2001012862A2 (en) | 1999-08-18 | 2001-02-22 | Illumina, Inc. | Compositions and methods for preparing oligonucleotide solutions |
AU2246601A (en) | 1999-08-30 | 2001-04-10 | Illumina, Inc. | Methods for improving signal detection from an array |
US7167615B1 (en) | 1999-11-05 | 2007-01-23 | Board Of Regents, The University Of Texas System | Resonant waveguide-grating filters and sensors and methods for making and using same |
US7582420B2 (en) | 2001-07-12 | 2009-09-01 | Illumina, Inc. | Multiplex nucleic acid reactions |
US20050214825A1 (en) * | 2000-02-07 | 2005-09-29 | John Stuelpnagel | Multiplex sample analysis on universal arrays |
ATE411397T1 (en) | 2000-02-07 | 2008-10-15 | Illumina Inc | NUCLEIC ACID DETECTION METHOD WITH UNIVERSAL PRIMING |
US6913884B2 (en) * | 2001-08-16 | 2005-07-05 | Illumina, Inc. | Compositions and methods for repetitive use of genomic DNA |
DE60127939T2 (en) | 2000-02-07 | 2008-01-24 | Illumina, Inc., San Diego | Nucleic acid detection method with universal priming |
US7361488B2 (en) * | 2000-02-07 | 2008-04-22 | Illumina, Inc. | Nucleic acid detection methods using universal priming |
US8076063B2 (en) | 2000-02-07 | 2011-12-13 | Illumina, Inc. | Multiplexed methylation detection methods |
US7955794B2 (en) * | 2000-09-21 | 2011-06-07 | Illumina, Inc. | Multiplex nucleic acid reactions |
US7611869B2 (en) * | 2000-02-07 | 2009-11-03 | Illumina, Inc. | Multiplexed methylation detection methods |
US6770441B2 (en) * | 2000-02-10 | 2004-08-03 | Illumina, Inc. | Array compositions and methods of making same |
AU2001239760B2 (en) * | 2000-02-10 | 2005-11-24 | Illumina, Inc. | Array of individual arrays as substrate for bead-based simultaneous processing of samples and manufacturing method therefor |
AU2001238389B2 (en) * | 2000-02-16 | 2006-09-21 | Illumina, Inc. | Parallel genotyping of multiple patient samples |
WO2002021128A2 (en) * | 2000-09-05 | 2002-03-14 | Illumina, Inc. | Cellular arrays comprising encoded cells |
US20040018491A1 (en) * | 2000-10-26 | 2004-01-29 | Kevin Gunderson | Detection of nucleic acid reactions on bead arrays |
US6686206B2 (en) * | 2001-04-04 | 2004-02-03 | Altair Center, Llc | Method of signal amplification in multi-chromophore luminescence sensors |
US6782290B2 (en) * | 2001-04-27 | 2004-08-24 | Medtronic, Inc. | Implantable medical device with rechargeable thin-film microbattery power source |
US20050267326A1 (en) * | 2001-10-02 | 2005-12-01 | Alfred E. Mann Institute For Biomedical Eng. At The University Of Southern California | Percutaneous chemical sensor based on fluorescence resonant energy transfer (FRET) |
US6984307B2 (en) * | 2001-10-05 | 2006-01-10 | Stephen Eliot Zweig | Dual glucose-hydroxybutyrate analytical sensors |
US7758744B2 (en) * | 2001-10-05 | 2010-07-20 | Stephen Eliot Zweig | Dual glucose-turbidimetric analytical sensors |
WO2003069333A1 (en) | 2002-02-14 | 2003-08-21 | Illumina, Inc. | Automated information processing in randomly ordered arrays |
US20040259105A1 (en) * | 2002-10-03 | 2004-12-23 | Jian-Bing Fan | Multiplex nucleic acid analysis using archived or fixed samples |
WO2004065000A1 (en) * | 2003-01-21 | 2004-08-05 | Illumina Inc. | Chemical reaction monitor |
US6943768B2 (en) | 2003-02-21 | 2005-09-13 | Xtellus Inc. | Thermal control system for liquid crystal cell |
US20060246576A1 (en) | 2005-04-06 | 2006-11-02 | Affymetrix, Inc. | Fluidic system and method for processing biological microarrays in personal instrumentation |
US9867530B2 (en) | 2006-08-14 | 2018-01-16 | Volcano Corporation | Telescopic side port catheter device with imaging system and method for accessing side branch occlusions |
US8280470B2 (en) * | 2006-11-03 | 2012-10-02 | Volcano Corporation | Analyte sensor method and apparatus |
WO2009009802A1 (en) | 2007-07-12 | 2009-01-15 | Volcano Corporation | Oct-ivus catheter for concurrent luminal imaging |
US9596993B2 (en) | 2007-07-12 | 2017-03-21 | Volcano Corporation | Automatic calibration systems and methods of use |
WO2009009799A1 (en) | 2007-07-12 | 2009-01-15 | Volcano Corporation | Catheter for in vivo imaging |
US11457842B2 (en) | 2008-01-15 | 2022-10-04 | Patient Shield Concepts, Llc | Method and apparatus for determining a deterioration of respiratory function |
DE102009005162A1 (en) * | 2009-01-15 | 2010-07-29 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Optic fiber sensor has a recess at the fiber end, on the optical axis, for a micro ball coated with sensor dyestuff to be bonded in place by an adhesive |
US9523701B2 (en) | 2009-07-29 | 2016-12-20 | Dynex Technologies, Inc. | Sample plate systems and methods |
GB0913258D0 (en) | 2009-07-29 | 2009-09-02 | Dynex Technologies Inc | Reagent dispenser |
US8694069B1 (en) | 2009-12-21 | 2014-04-08 | Kosense, LLC | Fiber-optic probe with embedded peripheral sensors for in-situ continuous monitoring |
ITFI20100237A1 (en) * | 2010-12-03 | 2012-06-04 | Consiglio Naz Delle Richerche | "OPTICAL FIBER PROBE AND USING SIZE OF MEASURING SENSOR" |
US11141063B2 (en) | 2010-12-23 | 2021-10-12 | Philips Image Guided Therapy Corporation | Integrated system architectures and methods of use |
US11040140B2 (en) | 2010-12-31 | 2021-06-22 | Philips Image Guided Therapy Corporation | Deep vein thrombosis therapeutic methods |
US9360630B2 (en) | 2011-08-31 | 2016-06-07 | Volcano Corporation | Optical-electrical rotary joint and methods of use |
US9292918B2 (en) | 2012-10-05 | 2016-03-22 | Volcano Corporation | Methods and systems for transforming luminal images |
US10568586B2 (en) | 2012-10-05 | 2020-02-25 | Volcano Corporation | Systems for indicating parameters in an imaging data set and methods of use |
US9307926B2 (en) | 2012-10-05 | 2016-04-12 | Volcano Corporation | Automatic stent detection |
US9324141B2 (en) | 2012-10-05 | 2016-04-26 | Volcano Corporation | Removal of A-scan streaking artifact |
US11272845B2 (en) | 2012-10-05 | 2022-03-15 | Philips Image Guided Therapy Corporation | System and method for instant and automatic border detection |
US9286673B2 (en) | 2012-10-05 | 2016-03-15 | Volcano Corporation | Systems for correcting distortions in a medical image and methods of use thereof |
JP2015532536A (en) | 2012-10-05 | 2015-11-09 | デイビッド ウェルフォード, | System and method for amplifying light |
US9367965B2 (en) | 2012-10-05 | 2016-06-14 | Volcano Corporation | Systems and methods for generating images of tissue |
US9858668B2 (en) | 2012-10-05 | 2018-01-02 | Volcano Corporation | Guidewire artifact removal in images |
US10070827B2 (en) | 2012-10-05 | 2018-09-11 | Volcano Corporation | Automatic image playback |
US9840734B2 (en) | 2012-10-22 | 2017-12-12 | Raindance Technologies, Inc. | Methods for analyzing DNA |
EP2931132B1 (en) | 2012-12-13 | 2023-07-05 | Philips Image Guided Therapy Corporation | System for targeted cannulation |
US10939826B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Aspirating and removing biological material |
US11406498B2 (en) | 2012-12-20 | 2022-08-09 | Philips Image Guided Therapy Corporation | Implant delivery system and implants |
EP2934310A4 (en) | 2012-12-20 | 2016-10-12 | Nathaniel J Kemp | Optical coherence tomography system that is reconfigurable between different imaging modes |
WO2014099899A1 (en) | 2012-12-20 | 2014-06-26 | Jeremy Stigall | Smooth transition catheters |
US10942022B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Manual calibration of imaging system |
CA2895770A1 (en) | 2012-12-20 | 2014-07-24 | Jeremy Stigall | Locating intravascular images |
US10413317B2 (en) | 2012-12-21 | 2019-09-17 | Volcano Corporation | System and method for catheter steering and operation |
US9486143B2 (en) | 2012-12-21 | 2016-11-08 | Volcano Corporation | Intravascular forward imaging device |
WO2014100162A1 (en) | 2012-12-21 | 2014-06-26 | Kemp Nathaniel J | Power-efficient optical buffering using optical switch |
EP2934323A4 (en) | 2012-12-21 | 2016-08-17 | Andrew Hancock | System and method for multipath processing of image signals |
EP2934280B1 (en) | 2012-12-21 | 2022-10-19 | Mai, Jerome | Ultrasound imaging with variable line density |
US9612105B2 (en) | 2012-12-21 | 2017-04-04 | Volcano Corporation | Polarization sensitive optical coherence tomography system |
EP2936426B1 (en) | 2012-12-21 | 2021-10-13 | Jason Spencer | System and method for graphical processing of medical data |
CA2896006A1 (en) | 2012-12-21 | 2014-06-26 | David Welford | Systems and methods for narrowing a wavelength emission of light |
WO2014100606A1 (en) | 2012-12-21 | 2014-06-26 | Meyer, Douglas | Rotational ultrasound imaging catheter with extended catheter body telescope |
US10058284B2 (en) | 2012-12-21 | 2018-08-28 | Volcano Corporation | Simultaneous imaging, monitoring, and therapy |
US10226597B2 (en) | 2013-03-07 | 2019-03-12 | Volcano Corporation | Guidewire with centering mechanism |
US9770172B2 (en) | 2013-03-07 | 2017-09-26 | Volcano Corporation | Multimodal segmentation in intravascular images |
US11154313B2 (en) | 2013-03-12 | 2021-10-26 | The Volcano Corporation | Vibrating guidewire torquer and methods of use |
EP2967391A4 (en) | 2013-03-12 | 2016-11-02 | Donna Collins | Systems and methods for diagnosing coronary microvascular disease |
US9301687B2 (en) | 2013-03-13 | 2016-04-05 | Volcano Corporation | System and method for OCT depth calibration |
US11026591B2 (en) | 2013-03-13 | 2021-06-08 | Philips Image Guided Therapy Corporation | Intravascular pressure sensor calibration |
US10758207B2 (en) | 2013-03-13 | 2020-09-01 | Philips Image Guided Therapy Corporation | Systems and methods for producing an image from a rotational intravascular ultrasound device |
US10219887B2 (en) | 2013-03-14 | 2019-03-05 | Volcano Corporation | Filters with echogenic characteristics |
US10292677B2 (en) | 2013-03-14 | 2019-05-21 | Volcano Corporation | Endoluminal filter having enhanced echogenic properties |
US20160030151A1 (en) | 2013-03-14 | 2016-02-04 | Volcano Corporation | Filters with echogenic characteristics |
CN104515771B (en) * | 2014-12-25 | 2017-10-17 | 贵州大学 | A kind of heavy metal fibre optical sensor based on spectrum development process and preparation method thereof |
US11478150B2 (en) * | 2016-03-28 | 2022-10-25 | Becton, Dickinson And Company | Optical fiber sensor |
US10835718B2 (en) | 2016-03-28 | 2020-11-17 | Becton, Dickinson And Company | Cannula with light-emitting optical fiber |
US10850046B2 (en) | 2016-03-28 | 2020-12-01 | Becton, Dickinson And Company | Cannula locator device |
US9689803B1 (en) * | 2016-04-20 | 2017-06-27 | Chroma Fish Corp. | Method and system for measuring a colorimetric characteristic of a sample and calibration of same |
CN108114347A (en) * | 2016-11-28 | 2018-06-05 | 爱本斯南京医疗器械有限公司 | A kind of injection device and its method of work with monitoring blood function |
RU182181U1 (en) * | 2018-04-14 | 2018-08-06 | федеральное государственное бюджетное образовательное учреждение высшего образования "Саратовский государственный медицинский университет имени В.И. Разумовского" Министерства здравоохранения Российской Федерации (ФГБОУ ВО Саратовский ГМУ им. В.И. Разумовского Минздрава России) | Device for intraoperative monitoring of regional hemoglobin oxygen saturation and vascular tone of the microvasculature |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4200110A (en) * | 1977-11-28 | 1980-04-29 | United States Of America | Fiber optic pH probe |
US4306877A (en) * | 1978-07-29 | 1981-12-22 | Max-Planck-Gesellschaft Zur Forderung Der Wissenschaften E.V. | Optical measurement of concentration |
EP0073558A2 (en) * | 1981-08-25 | 1983-03-09 | THE UNITED STATES OF AMERICA as represented by the Secretary United States Department of Commerce | Fiber optic pH probe for tissue measurements |
Family Cites Families (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3123066A (en) * | 1964-03-03 | brumley | ||
US3068742A (en) * | 1959-06-15 | 1962-12-18 | American Optical Corp | Means for performing colorimetry |
US3814081A (en) * | 1971-04-02 | 1974-06-04 | Olympus Optical Co | Optical measuring catheter |
JPS6034750B2 (en) * | 1977-03-10 | 1985-08-10 | 株式会社リコー | Developer remaining amount detection device |
US4344438A (en) * | 1978-08-02 | 1982-08-17 | The United States Of America As Represented By The Department Of Health, Education And Welfare | Optical sensor of plasma constituents |
JPS5537934A (en) * | 1978-09-09 | 1980-03-17 | Yoshihana Matsushima | Engine oil checker |
DE2856188C2 (en) * | 1978-12-27 | 1985-09-05 | Brown, Boveri & Cie Ag, 6800 Mannheim | Device for the detection of arcing faults in switchgear |
JPS56124036A (en) * | 1981-01-26 | 1981-09-29 | Sumitomo Electric Ind Ltd | Spectroanalytic device for diagnosis of morbidity |
JPS57199943A (en) * | 1981-06-03 | 1982-12-08 | Hitachi Ltd | Measuring device for wetness of steam |
JPS59154340A (en) * | 1983-02-23 | 1984-09-03 | Mitsubishi Heavy Ind Ltd | Wetness measuring device |
EP0126600B1 (en) * | 1983-05-17 | 1989-03-01 | Elf U.K. Plc | Optical fibre probe |
JPS6039536A (en) * | 1983-08-12 | 1985-03-01 | Hochiki Corp | Gas sensor |
-
1985
- 1985-08-06 US US06/763,019 patent/US4682895A/en not_active Expired - Lifetime
-
1986
- 1986-07-31 JP JP61504393A patent/JPH0697206B2/en not_active Expired - Lifetime
- 1986-07-31 DE DE8686905053T patent/DE3667541D1/en not_active Expired - Fee Related
- 1986-07-31 WO PCT/US1986/001579 patent/WO1987000920A1/en active IP Right Grant
- 1986-07-31 EP EP86905053A patent/EP0232369B1/en not_active Expired
- 1986-08-05 CN CN86106159A patent/CN1009955B/en not_active Expired
- 1986-08-05 CA CA000515301A patent/CA1292665C/en not_active Expired - Fee Related
-
1987
- 1987-04-03 RU SU874202483A patent/RU1830141C/en active
- 1987-04-06 KR KR870700296A patent/KR880700259A/en not_active Application Discontinuation
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4200110A (en) * | 1977-11-28 | 1980-04-29 | United States Of America | Fiber optic pH probe |
US4306877A (en) * | 1978-07-29 | 1981-12-22 | Max-Planck-Gesellschaft Zur Forderung Der Wissenschaften E.V. | Optical measurement of concentration |
EP0073558A2 (en) * | 1981-08-25 | 1983-03-09 | THE UNITED STATES OF AMERICA as represented by the Secretary United States Department of Commerce | Fiber optic pH probe for tissue measurements |
Non-Patent Citations (1)
Title |
---|
PATENTS ABSTRACTS OF JAPAN, Volume 4, No. 70 (P-12) (552), 23 May 1980, & JP, A, 5537934 (Y. Matsushima) see the whole Abstract * |
Cited By (18)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0234928A2 (en) * | 1986-02-27 | 1987-09-02 | Eli Lilly And Company | Optical fiber apparatus |
EP0234928A3 (en) * | 1986-02-27 | 1989-05-10 | Eli Lilly And Company | Optical fiber apparatus |
EP0352610A2 (en) * | 1988-07-25 | 1990-01-31 | Abbott Laboratories | Fiber-optic physiological probes |
EP0352610A3 (en) * | 1988-07-25 | 1990-11-28 | Abbott Laboratories | Fiber-optic physiological probes |
WO1991018306A2 (en) * | 1990-05-22 | 1991-11-28 | Optex Biomedical, Inc. | Optical probe |
WO1991018306A3 (en) * | 1990-05-22 | 1992-02-06 | Optex Biomedical Inc | Optical probe |
AU645323B2 (en) * | 1990-05-22 | 1994-01-13 | Optex Biomedical, Inc. | Optical probe |
EP0579257A1 (en) * | 1992-07-17 | 1994-01-19 | ULTRAKUST electronic GmbH | Device for determining optical spectral shifts caused by physical or chemical effects |
WO1994010554A1 (en) * | 1992-10-23 | 1994-05-11 | Optex Biomedical, Inc. | Method of making an optical fibre sensor probe |
WO1994010553A1 (en) * | 1992-10-23 | 1994-05-11 | Optex Biomedical, Inc. | Fibre-optic probe for the measurement of fluid parameters |
GB2283567A (en) * | 1993-10-29 | 1995-05-10 | Univ Brunel | Fibre optic sensor device |
GB2283567B (en) * | 1993-10-29 | 1998-03-18 | Univ Brunel | Optical sensor device |
WO2008098087A3 (en) * | 2007-02-06 | 2008-11-27 | Glumetrics Inc | Optical systems and methods for rationmetric measurement of blood glucose concentration |
US7751863B2 (en) | 2007-02-06 | 2010-07-06 | Glumetrics, Inc. | Optical determination of ph and glucose |
US8838195B2 (en) | 2007-02-06 | 2014-09-16 | Medtronic Minimed, Inc. | Optical systems and methods for ratiometric measurement of blood glucose concentration |
US8983565B2 (en) | 2007-02-06 | 2015-03-17 | Medtronic Minimed, Inc. | Optical determination of pH and glucose |
US9839378B2 (en) | 2007-02-06 | 2017-12-12 | Medtronic Minimed, Inc. | Optical systems and methods for ratiometric measurement of blood glucose concentration |
US8979790B2 (en) | 2007-11-21 | 2015-03-17 | Medtronic Minimed, Inc. | Use of an equilibrium sensor to monitor glucose concentration |
Also Published As
Publication number | Publication date |
---|---|
KR880700259A (en) | 1988-02-22 |
US4682895A (en) | 1987-07-28 |
EP0232369A1 (en) | 1987-08-19 |
DE3667541D1 (en) | 1990-01-18 |
CN1009955B (en) | 1990-10-10 |
RU1830141C (en) | 1993-07-23 |
JPH0697206B2 (en) | 1994-11-30 |
CN86106159A (en) | 1987-06-03 |
CA1292665C (en) | 1991-12-03 |
JPS63500737A (en) | 1988-03-17 |
EP0232369B1 (en) | 1989-12-13 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP0232369B1 (en) | Fiber optic probe for quantification of colorimetric reactions | |
US4710623A (en) | Optical fiber catheter with fiber-contained reactive element | |
US5047208A (en) | Blood gas monitoring sensors | |
US5119463A (en) | Compound optical probe employing single optical waveguide | |
EP0909946A3 (en) | Chemical sensing techniques employing liquid-core optical fibers | |
US4752115A (en) | Optical sensor for monitoring the partial pressure of oxygen | |
CA1281219C (en) | Evanescent wave sensors | |
US5335305A (en) | Optical sensor for fluid parameters | |
US4900381A (en) | Method for manufacturing a measuring probe | |
CA1325908C (en) | Modular fiber optic chemical sensor | |
EP0073558A3 (en) | Fiber optic ph probe for tissue measurements | |
EP0481740A2 (en) | Optical fiber PH microsensor and method of manufacture | |
GB2284904B (en) | Rigid aqueous fluid core light guide and applications therefor | |
EP0335725A3 (en) | Apparatus and method for detection of fluorescence or light scatter | |
US4943364A (en) | Fiber optic CO2 sensor | |
CN101776493B (en) | Optical fiber temperature/humidity sensor inductive layer and preparation method and application thereof | |
JPH01107737A (en) | Optical fiber probe connector for physiological measuring apparatus | |
US5251633A (en) | Optical probe | |
JPS6189528A (en) | Waveguide used for spectral analysis measuring device and mesuring method using said waveguide | |
JP3305398B2 (en) | Optical fiber sensor | |
EP0215854A1 (en) | Fibre optic chemical sensor | |
JP2732878B2 (en) | Optical fiber sensor | |
Schultz et al. | [32] Optical fiber affinity sensors | |
EP0136887A3 (en) | Dielectric optical fibre cable | |
DE202006011421U1 (en) | Fiber optic sensor for pH measurement, has sensor head with area covered with thin sensitive layer of copolymer, where layer has high refractive index and forms micro environment for coloring material and reaches refractive index of core |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): JP KR SU |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): AT BE CH DE FR GB IT LU NL SE |
|
WWE | Wipo information: entry into national phase |
Ref document number: 1986905053 Country of ref document: EP |
|
WWP | Wipo information: published in national office |
Ref document number: 1986905053 Country of ref document: EP |
|
WWG | Wipo information: grant in national office |
Ref document number: 1986905053 Country of ref document: EP |