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WO2013046993A1 - Capteur d'aiguille et unité de capteur d'aiguille - Google Patents

Capteur d'aiguille et unité de capteur d'aiguille Download PDF

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Publication number
WO2013046993A1
WO2013046993A1 PCT/JP2012/070881 JP2012070881W WO2013046993A1 WO 2013046993 A1 WO2013046993 A1 WO 2013046993A1 JP 2012070881 W JP2012070881 W JP 2012070881W WO 2013046993 A1 WO2013046993 A1 WO 2013046993A1
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WO
WIPO (PCT)
Prior art keywords
needle
sensor
layer
sensor unit
disposed
Prior art date
Application number
PCT/JP2012/070881
Other languages
English (en)
Japanese (ja)
Inventor
貴平 時本
利夫 深井
Original Assignee
オリンパス株式会社
テルモ株式会社
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 オリンパス株式会社, テルモ株式会社 filed Critical オリンパス株式会社
Publication of WO2013046993A1 publication Critical patent/WO2013046993A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/1459—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters invasive, e.g. introduced into the body by a catheter
    • 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
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters

Definitions

  • the present invention relates to a needle-type sensor for measuring the concentration of an analyte in a body and a needle-type sensor unit having the needle-type sensor, and in particular, a short-term indwelling needle-type sensor in which a sensor unit is inserted and indwelled, and the above-mentioned
  • the present invention relates to a needle type sensor unit having a needle type sensor.
  • an analyte of body fluid or blood in the body that is, a sensor unit for measuring the concentration of the substance to be measured is inserted and placed in the body.
  • the short-term indwelling needle sensor continuously measures the concentration of the analyte in the body for a predetermined period, for example, one week.
  • US Pat. No. 7,003336 discloses a needle-type sensor unit 101 in which a needle-type sensor 130 having a sensor portion 110 at the tip is inserted into a slot 150 that is a sheath tube. ing.
  • the needle-type sensor unit 101 includes a sensor of the needle-type sensor 130 by removing the slot 150 from the subject 90 after the slot 150 and the needle-type sensor 130 are punctured into the subject 90. Part 110 is placed in the body.
  • the size D91 of the hole 91 formed in the subject 90 by puncturing the slot 150 is substantially equal to the outer dimension of the slot 150. That is, the size D91 of the hole 91 is larger than the outer dimension D110 of the needle sensor 130. For this reason, at the start of use, that is, immediately after the slot 150 is removed, the sensor unit 110 of the needle sensor 130 is not in contact with the surrounding tissue inside the hole 91. Since the hole 91 gradually contracts due to biological activity, the sensor unit 110 eventually comes into contact with surrounding tissue.
  • the sensor unit 110 detects an analyte by contact with a body fluid or the like that has oozed into the hole 91 even in a non-contact state with the tissue.
  • the non-contact state is more responsive to changes in the analyte concentration than the contact state.
  • the contact state may be temporarily changed from the non-contact state. For this reason, the needle-type sensor 130 may not be easily measured for a while from the start of use.
  • An object of the present invention is to provide a needle type sensor capable of performing stable measurement from the start of use and a needle type sensor unit having the needle type sensor.
  • the needle sensor includes a main body portion, a connector portion provided on a proximal end side of the main body portion, and a sensor portion for measuring an analyte concentration provided on a distal end side of the main body portion.
  • a swelling layer that absorbs and swells the liquid component of the subject is disposed on at least a part of the outer peripheral surface of the tip portion including the measurement surface of the sensor portion. ing.
  • the needle-type sensor unit includes a main body part, a connector part provided on the base end side of the main body part, and an analyte concentration provided on the distal end side of the main body part.
  • a swelling layer that absorbs and swells the liquid component of the subject is disposed on at least a part of the outer peripheral surface of the tip portion including the measurement surface of the sensor portion.
  • a needle-type sensor An outer dimension of the tip including the swollen swelling layer, which is punctured in the subject with the tip housed therein, and is removed while leaving the tip in the body before starting the measurement of the analyte concentration.
  • a sheath tube having a smaller outer dimension than the outer tube.
  • the needle-type sensor unit 1 includes a sensor 30 and a sheath tube 50 for puncturing.
  • the sheath tube 50 is a hollow so-called outer needle having a sharp tip, and is an auxiliary tool for puncturing the subject with the sensor 30. That is, the sheath tube 50 has at least the distal end portion 32 of the sensor 30 in the hollow portion. The subject is punctured in a state in which it is accommodated. And before starting the measurement of the analyte concentration, the sensor tube 30 is left in the body and the sheath tube 50 is removed.
  • the sensor 30 includes a distal end portion 32, a main body portion 33 extending from the distal end portion 32, and a connector portion 35 extending from the main body portion 33.
  • the distal end portion 32, the main body portion 33, and the connector portion 35 are produced, for example, by processing a silicon substrate.
  • the boundary between the distal end portion 32 and the main body portion 33 may not be clear.
  • a region where the sensor unit 10 at the tip of the sensor 30 is disposed is referred to as a tip 32.
  • the elongate sheath tube 50 has a substantially C-shaped cross section in the direction perpendicular to the major axis, and has an elongated slit in the major axis direction.
  • the dimensions d50 and dW50 of the hollow portion of the sheath tube 50 are larger than the outer dimensions D32 and DW32 of the distal end portion 32, respectively.
  • the dimension of the hollow part and the outer dimension of the tip part 32 are cross-sectional dimensions (dimensions in plan view) in the direction perpendicular to the major axis, and the shape in plan view is a diameter in the case of a circle.
  • the lengths are the lengths of the two sides, but for the sake of simplicity, the length of one side will be described as an example.
  • the measurement surface of the light shielding layer 18 (see FIG. 7) of the sensor unit 10 for measuring the analyte concentration is exposed at a part of the front surface 32 of the sensor 30. Further, the outer peripheral surface on the opposite side across the surface of the sensor portion 10 of the tip portion 32 where the light shielding layer 18 is exposed and the central axis in the major axis direction, in other words, the outer peripheral surface on the back side with respect to the measurement surface of the sensor portion 10 A swelling layer 60 is disposed on the surface.
  • the swelling layer 60 should just be arrange
  • the swelling layer 60 swells by absorbing the liquid of the subject, that is, water in the body, but is in a dry and contracted state in a state where it is accommodated in the hollow portion of the sheath tube 50 for puncture. .
  • the sensor 30 is used as the sensor system 2 in combination with the sensor main body 40 and the receiver 45. That is, the sensor system 2 includes a sensor 30, a sensor main body 40, and a receiver 45 that receives and stores a signal from the sensor main body 40.
  • the connector part 35 of the sensor 30 is detachably fitted to the fitting part 41 of the sensor main body part 40.
  • the sensor 30 is electrically connected to the sensor body 40 by mechanically fitting the connector part 35 with the fitting part 41 of the sensor body 40. Transmission / reception of signals between the sensor body 40 and the receiver 45 is performed wirelessly or by wire.
  • the sensor body 40 includes a wireless antenna for wirelessly transmitting and receiving signals to and from the receiver 45, a power source such as a battery, and various circuits for driving and controlling the sensor unit 10.
  • the various circuits include an amplifier circuit that amplifies signals, a circuit reference clock generation circuit, a logic circuit, a data processing circuit, an AD conversion processing circuit, a mode control circuit, a memory circuit, and a communication high-frequency generator circuit. be able to.
  • the sensor main body 40 when transmitting and receiving a signal with the receiver 45 by wire, the sensor main body 40 has a signal line instead of the wireless antenna. Information such as the analyte concentration in the body fluid measured by the sensor unit 10 is stored in the memory of the receiver 45.
  • the sensor 30 is a disposable part that is disposed of after use to prevent infection, but the sensor body 40 and the receiver 45 are reusable parts that are repeatedly reused.
  • the sensor unit 10 includes a silicon substrate as a substrate 11, a photoelectric conversion element (PD element) 12, a silicon oxide layer (not shown), a filter layer 14, and a light emitting element (LED that generates excitation light and transmits fluorescence).
  • PD element photoelectric conversion element
  • LED light emitting element
  • (Element) 15 a transparent intermediate layer 16, an indicator layer 17 containing a fluorescent dye, and a light-shielding layer 18 that is the outermost layer are sequentially laminated from the substrate 11 side. Further, at least a part of each of the PD element 12, the filter layer 14, the LED element 15, and the indicator layer 17 is formed in the same region on the substrate 11.
  • the LED element 15, the transparent intermediate layer 16, and the indicator layer 17 are accommodated inside the sensor frame 20.
  • the surface other than the light shielding layer 18 is covered with a protective layer 19 made of polyparaxylylene or the like having high biocompatibility.
  • a PD element 12 that converts received fluorescence into an electrical signal is formed.
  • the substrate 11 can be thinned to about several tens of ⁇ m in the manufacturing process.
  • the photoelectric conversion element a photodiode or a phototransistor is particularly preferable. This is because the fluorescence detection sensitivity having high sensitivity and excellent stability can be realized, and as a result, the sensor unit 10 having excellent detection sensitivity and detection accuracy can be realized.
  • the filter layer 14 that covers the light receiving surface of the PD element 12 is, for example, an absorption optical filter that blocks the excitation light E generated by the LED element 15 and transmits fluorescence F having a longer wavelength.
  • the filter layer 14 is preferably a silicon layer such as polycrystalline silicon, a silicon carbide layer, or a gallium phosphide layer. All of the above materials have a low transmittance at a wavelength of excitation light shorter than 375 nm and a high transmittance at a wavelength of fluorescence of 460 nm, that is, a transmittance selection of 6 digits or more as a ratio of the transmittance of excitation light to the transmittance of fluorescence. Have sex.
  • the LED element 15 is a light emitting element that emits excitation light and transmits fluorescence.
  • a light-emitting element a sapphire substrate is used from the viewpoints of fluorescence transmittance, light generation efficiency, wide wavelength selectivity of excitation light, and little emission of light having a wavelength other than ultraviolet light serving as excitation light.
  • a gallium nitride based ultraviolet LED is preferable.
  • the indicator layer 17 generates fluorescence with a light amount corresponding to the concentration of the analyte by the interaction with the entering analyte and the excitation light.
  • the thickness of the indicator layer 17 is set to about several tens of ⁇ m.
  • the indicator layer 17 is made of a base material containing a fluorescent dye that generates fluorescence having an intensity corresponding to the amount of the analyte, that is, the concentration of the analyte in the sample.
  • Any fluorescent dye can be used as long as it is selected by the analyte and the amount of fluorescent light reversibly changes in accordance with the amount of the analyte.
  • the residual fluorescence A crown ether derivative having a group can be used.
  • substances that reversibly bind to glucose such as a ruthenium organic complex, a fluorescent phenylboronic acid derivative, or a glucose binding protein modified with fluorescein, can be used as a fluorescent dye.
  • Etc. can be particularly preferably used.
  • organic complexes such as osmium, iridium, rhodium, rhenium and chromium can be used instead of ruthenium in the ruthenium organic complex.
  • a fluorescent phenylboronic acid derivative containing two phenylboronic acids and anthracene as a fluorescent residue has high detection sensitivity.
  • the sensor unit 10 can correspond to various uses such as an oxygen sensor, a glucose sensor, a pH sensor, an immunosensor, or a microorganism sensor by selecting a fluorescent dye.
  • the indicator layer 17 preferably includes a hydrogel containing or binding the fluorescent dye.
  • a hydrogel containing or binding the fluorescent dye For example, it is easy to contain water such as polysaccharides such as methylcellulose or dextran, acrylic hydrogel prepared by polymerizing monomers such as acrylamide, methylolacrylamide, and hydroxyethyl acrylate, or urethane hydrogel prepared from polyethylene glycol and diisocyanate.
  • the indicator layer 17 is formed by including a fluorescent dye in the material.
  • the characteristics of the indicator layer 17 made of hydrogel may change with time before use in a water-containing state. For this reason, it is preferable that the indicator is in a dry state before use and in a water-containing state at the start of use.
  • the dried hydrogel constituting the indicator layer 17 When the dried hydrogel constituting the indicator layer 17 is inserted into the body at the start of use, it absorbs a body fluid such as blood, that is, water, through the light shielding layer 18, and swells.
  • the light shielding layer 18 made of, for example, hydrogel containing carbon black or the like is disposed on the indicator layer 17, that is, as the outermost layer constituting the measurement surface of the sensor unit 10.
  • the light shielding layer 18 has the property of blocking external light and excitation light, and the property of allowing analyte and water to pass through.
  • tip part 32 consists of the same hydrogel as the indicator layer 17, and is a dry state before use start.
  • Hydrogel swells when it absorbs water, that is, its volume increases. In other words, the hydrous hydrogel shrinks when dried.
  • a water-containing hydrogel having a polymer component of about 10% will have a volume of 50% to 10% of the water content when dried.
  • the swelling layer 60 comes into contact with a body fluid that is a liquid component of the specimen, and the swelling layer 60 absorbs the body fluid and swells. .
  • the outer dimensions D50 and DW50 of the sheath tube 50 are larger than the outer dimensions D32 and DW32 of the distal end portion 32 of the sensor 30 in the needle type sensor unit 1. .
  • the size of the hole 91 formed inside the subject by the sheath tube 50 is equal to the outer dimension of the sheath tube 50. For this reason, the sensor unit 10 is not in contact with the surrounding tissue inside the hole 91 and is in an unstable state.
  • the swelling layer 60 absorbs water and swells in a short time, the sensor unit 10 comes into contact with the tissue and becomes stable. That is, the sensor unit 10 including the swelling layer 60 can be accommodated in a hollow portion that is narrower than the outer dimension of the sheath tube 50 in a dry and contracted state. It becomes larger than the size.
  • the amount of change in the thickness of the swelling layer 60 before and after swelling is larger than the difference between the outer dimension of the sheath tube 50 and the outer dimension of the sensor unit 10.
  • the time required for the swelling layer 60 to swell to a predetermined size is much shorter than the time required for the pores 91 to contract due to biological activity. For this reason, for example, at the start of use after several minutes from the removal of the sheath tube 50, the sensor unit 10 comes into stable contact with the surrounding tissue.
  • the sensor unit 10 Since the sensor unit 10 is in stable contact with surrounding tissue from the start of use, the sensor 30 can perform stable measurement. Further, the needle-type sensor unit 1 including the sensor 30 can perform stable measurement from the start of use.
  • tip part 32 is the distance of the surface where the light shielding layer 18 of the sensor part 10 was exposed, and the surface of the swelling layer 60, and the outer dimension of the sheath tube 50 is the longest outer dimension.
  • the outer dimension is the length of the long side.
  • the outer dimension when the cross section is circular is the outer diameter.
  • the dry state of the hydrogel constituting the swelling layer 60 does not mean that the moisture content is 0 wt%. If there is a change due to swelling sufficient to close the gap between the hole 91 and the sensor unit 10, a small amount of water is required. Or a plasticizer such as glycerin.
  • the water content is the weight of hydrogel (water content 100%) which has been immersed in water for 1 hour and swollen, and the hydrogel (water content 0%) heated at 100 ° C. for 12 hours in dry air or nitrogen. %) And the weight of the hydrogel to be measured (moisture content X%).
  • the correction is performed so that the hydrogel has the same weight.
  • the water content is 30 wt% when the weight difference between the hydrogel to be measured and the hydrogel having a water content of 0% is 30 mg.
  • the swelling layer 60 and the indicator layer 17 of the sensor 30 before use preferably have a moisture content of 1 wt% to 25 wt%, and particularly preferably 5 wt% to 10 wt%. If it is more than the said range, the water absorption speed of the swelling layer 60 will not fall, and if it is less than the said range, while being able to perform the stable measurement from the start of use, the characteristic deterioration by the time-dependent change of an indicator can be prevented.
  • the indicator layer 17 when the indicator layer 17 is also inserted into the body at the start of use, it absorbs water and swells. For this reason, as shown in FIG. 10, since the surface of the sensor part 10 becomes convex shape, the stable measurement can be performed in a shorter time. In addition, when the light shielding layer 18 consists of hydrogel, the light shielding layer 18 will also swell.
  • a sensor 30A according to a second embodiment of the present invention will be described with reference to FIG. Since the sensor 30A of this embodiment is similar to the sensor 30 of the first embodiment, the same components are denoted by the same reference numerals, and description thereof is omitted.
  • the swelling layer 60 ⁇ / b> A through which the analyte can pass is disposed on the entire outer peripheral surface of the tip portion 32 ⁇ / b> A including the surface of the light shielding layer 18. .
  • the swelling layer 60A can be so-called dip-coated by, for example, immersing and pulling up the tip 32A of the sensor 30A in a heated hydrogel solution. Since the coated swelling layer 60A is in a water-containing state, it is dried until a desired water content is obtained.
  • the thickness of the swelling layer 60A is half the thickness of the swelling layer 60 of the sensor 30 of the first embodiment, and has the same level of effect. For this reason, the swelling layer 60A is not only easy to form, but also rapidly expands due to water absorption. Furthermore, since the swelling layer 60A disposed on the sensor unit 10 and the swelling layer 60A disposed on the opposite side of the sensor unit 10 swell at the same time, the sensor unit 10 becomes stable. The time required for the sensor 30 ⁇ / b> A is half that of the sensor 30.
  • the sensor 30A has the effect of the sensor 30 and can perform stable measurement in a shorter time.
  • the sensor 30A is easy to manufacture because the swelling layer 60A can be formed by dip coating.
  • the sensor 30B of the needle sensor unit 1B has a sensor unit 10B having a vertical structure.
  • a concave portion having a rectangular opening in plan view is formed in a substrate 11 made of a semiconductor such as silicon.
  • the PD element 12B is formed on the wall surface (side surface) of the recess, and the LED element 15B is disposed on the bottom surface of the recess. That is, in the sensor unit having the vertical structure, the PD element 12B is formed in the vertical direction with respect to the main surface.
  • transmits fluorescence is arrange
  • the opening surface of the recess is wider than the bottom surface, and the side surface is not perpendicular to the bottom surface but is inclined at a predetermined angle ⁇ .
  • substrate 11 which has a recessed part may be produced by joining the frame-shaped sensor frame board
  • a dried indicator layer 17B is disposed on the transparent intermediate layer 16B covering the LED element 15B.
  • the light shielding layer 18B which interrupts external light is arrange
  • the surface of the light shielding layer 18B is a measurement surface.
  • the swelling layer 60B is arrange
  • the sensor unit 10B has a recess having a bottom surface parallel to the main surface, and the light receiving surfaces of the PD element 12B and the PD element 12B that convert fluorescence into an electric signal are formed on the inner wall of the recess.
  • the light When the light is received, it has an indicator layer 17B that emits fluorescence with a light amount corresponding to the analyte concentration, and a light shielding layer 18B through which the analyte that prevents the entry of external light can pass.
  • the sensor 30B When the sensor 30B is inserted into the body, the body fluid containing the analyte is absorbed by the swelling layer 60B and the indicator layer 17B. For this reason, the sensor 30B has the same effect as the sensor 30 shown in FIG. Further, the sensor 30B is easier to miniaturize than the sensor 30 and is more sensitive.
  • the senor 30B Next, a method for manufacturing the sensor 30B will be briefly described. In addition, although it may manufacture for every sensor 30B, it is preferable to manufacture many sensors collectively as a wafer process.
  • a mask layer having a plurality of rectangular mask patterns in plan view is manufactured on the first main surface of a silicon wafer to be a substrate 11 having an area where a plurality of needle sensors can be manufactured. Then, a plurality of recesses having a bottom surface parallel to the first main surface is formed by an etching method.
  • the etching method is preferably a wet etching method using a tetramethylammonium hydroxide aqueous solution or a potassium hydroxide aqueous solution, but a dry etching method such as reactive ion etching or chemical dry etching may also be used.
  • the etching speed of the (111) plane is anisotropic etching compared to the (100) plane.
  • the angle with the (100) plane (bottom plane) is 54.7 degrees.
  • the PD element 12B is formed on the four side surfaces of each recess by a known semiconductor process.
  • the concave portion whose side surface is inclined has a larger area in which the PD element 12 can be formed than the concave portion whose vertical side surface is vertical, and the PD element 12B can be easily formed on the side surface. If the inclination angle of the side surface is 30 to 70 degrees, the above effect is remarkable.
  • the filter layer 14B is disposed on the side PD element 12B.
  • the LED elements 15B are disposed on the bottom surfaces of the plurality of recesses. Further, after forming the transparent intermediate layer 16B so as to cover the LED element 15B, a buffer solution that becomes the indicator layer 17B is filled in the recess. Further, a light shielding layer 18B is disposed so as to cover the opening of the recess. Then, the silicon wafer on which a plurality of sensors are formed is singulated. Furthermore, the swelling layer 60B is disposed on the tip portion 32B by the dip coating method, and the sensor portion 10B is completed through a hydrogel drying process.
  • the substrate 11 may be a main constituent member of the tip portion 32B, the main body portion 33, and the connector portion 35. That is, not only the tip portion 32B having the sensor portion 10B but also the main body portion 33 and the connector portion 35 may be manufactured by processing a silicon wafer.
  • the sensor 30B is easy to manufacture because the sensor unit 10B is formed in the recess formed in the substrate 11.

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  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Optics & Photonics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention concerne un capteur (30) qui comprend : un corps principal (33) ; un raccord (35), qui est disposé sur l'extrémité de base du corps principal ; et une pointe (32), qui est disposée sur la pointe du corps principal (33) et sur laquelle une partie de capteur (10) pour mesurer la concentration d'un analyte est disposée. Sur au moins une partie de la surface externe de la pointe (32), qui comprend la surface de mesure de la partie de capteur (10), une couche de gonflement (60) qui absorbe un fluide corporel et gonfle, est disposée.
PCT/JP2012/070881 2011-09-30 2012-08-17 Capteur d'aiguille et unité de capteur d'aiguille WO2013046993A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2011-215815 2011-09-30
JP2011215815 2011-09-30

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Publication Number Publication Date
WO2013046993A1 true WO2013046993A1 (fr) 2013-04-04

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2021028544A1 (fr) * 2019-08-13 2021-02-18 B. Braun Melsungen Ag Récipient d'échantillonnage médical comportant un champ d'essai et une unité d'absorption
JP7560153B2 (ja) 2019-12-27 2024-10-02 エイシーズ メディカル エルエルシー 医療機器のためのリアルタイム蛍光検出システム

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2005279285A (ja) * 2000-02-10 2005-10-13 Medtronic Minimed Inc 改良された検体センサ
JP2009544409A (ja) * 2006-07-26 2009-12-17 メドトロニック ミニメド インコーポレイテッド アナライトセンサーを安定化させるための方法および材料
WO2010119916A1 (fr) * 2009-04-13 2010-10-21 Olympus Corporation Capteur de fluorescence, capteur de fluorescence de type aiguille et procédé pour mesurer un analyte

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2005279285A (ja) * 2000-02-10 2005-10-13 Medtronic Minimed Inc 改良された検体センサ
JP2009544409A (ja) * 2006-07-26 2009-12-17 メドトロニック ミニメド インコーポレイテッド アナライトセンサーを安定化させるための方法および材料
WO2010119916A1 (fr) * 2009-04-13 2010-10-21 Olympus Corporation Capteur de fluorescence, capteur de fluorescence de type aiguille et procédé pour mesurer un analyte

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2021028544A1 (fr) * 2019-08-13 2021-02-18 B. Braun Melsungen Ag Récipient d'échantillonnage médical comportant un champ d'essai et une unité d'absorption
JP7560153B2 (ja) 2019-12-27 2024-10-02 エイシーズ メディカル エルエルシー 医療機器のためのリアルタイム蛍光検出システム

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