WO1993001489A1 - Detecteur portatif de glucose - Google Patents

Detecteur portatif de glucose Download PDF

Info

Publication number
WO1993001489A1
WO1993001489A1 PCT/DK1992/000213 DK9200213W WO9301489A1 WO 1993001489 A1 WO1993001489 A1 WO 1993001489A1 DK 9200213 W DK9200213 W DK 9200213W WO 9301489 A1 WO9301489 A1 WO 9301489A1
Authority
WO
WIPO (PCT)
Prior art keywords
enzyme
sample
measuring
reactor
buffer
Prior art date
Application number
PCT/DK1992/000213
Other languages
English (en)
Inventor
Bengt Danielsson
Original Assignee
Novo Nordisk A/S
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
Priority claimed from DK134591A external-priority patent/DK134591D0/da
Priority claimed from DK164691A external-priority patent/DK164691D0/da
Application filed by Novo Nordisk A/S filed Critical Novo Nordisk A/S
Priority to EP92916171A priority Critical patent/EP0594773A1/fr
Publication of WO1993001489A1 publication Critical patent/WO1993001489A1/fr

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N25/00—Investigating or analyzing materials by the use of thermal means
    • G01N25/20—Investigating or analyzing materials by the use of thermal means by investigating the development of heat, i.e. calorimetry, e.g. by measuring specific heat, by measuring thermal conductivity
    • G01N25/48—Investigating or analyzing materials by the use of thermal means by investigating the development of heat, i.e. calorimetry, e.g. by measuring specific heat, by measuring thermal conductivity on solution, sorption, or a chemical reaction not involving combustion or catalytic oxidation
    • G01N25/4873—Investigating or analyzing materials by the use of thermal means by investigating the development of heat, i.e. calorimetry, e.g. by measuring specific heat, by measuring thermal conductivity on solution, sorption, or a chemical reaction not involving combustion or catalytic oxidation for a flowing, e.g. gas sample
    • G01N25/4893—Investigating or analyzing materials by the use of thermal means by investigating the development of heat, i.e. calorimetry, e.g. by measuring specific heat, by measuring thermal conductivity on solution, sorption, or a chemical reaction not involving combustion or catalytic oxidation for a flowing, e.g. gas sample by using a differential method

Definitions

  • the invention relates to a portable apparatus for measuring the concentration of a substance in a body fluid, e.g. for measuring the glucose level in the blood.
  • a portable apparatus for measuring the concentration of a substance in a body fluid, e.g. for measuring the glucose level in the blood.
  • a device should have dimensions not much bigger than those of a king size pack of cigarettes, i. e. about 20 x 50 x 100 mm.
  • an apparatus must have dimensions as stated, it must permit measurements on samples of unprepared blood, that is if any preparation of the sample has to be made it must be made automatically inside the apparatus, the needed size of the sample should not exceed 25 ⁇ l corresponding to a drop of blood which may be provided by pricking a finger or an earlobe, and the apparatus should be able to perform a great number of measurements, say 100, before services are needed in the form of replacing consumed articles.
  • Portable glucose sensors are known which are based on colouring of a strip when the glucose in a sample placed on the strip is oxidized using an enzyme. The colouring is evaluated by visual inspection or using a miniaturized photometer. However, the presence of the blood cells in the sample makes the result unprecise.
  • glucose sensors are based on the use of amperometric sensors measuring oxygen consumption or hydrogen peroxide production when glucose is oxidized in the presence of glucose oxidase.
  • amperometric sensors measuring oxygen consumption or hydrogen peroxide production when glucose is oxidized in the presence of glucose oxidase.
  • the use of amperometric sensors causes problems as large drift, short lifetime, difficulties with calibration, lack of accuracy, and various interferences.
  • a portable glucose sensor for measuring the glucose content in a blood sample, which according to the invention is characterized in that the measuring means is of a type measuring the heat production when the glucose in the sample is decomposed in the presence of an enzyme.
  • the measuring means may be an enzyme calorimeter comprising a reactor containing an enzyme carrier material on the surface of which an enzyme is immobilized, an inlet and an outlet for liquid and a pair of thermosensors measuring the temperature increase of a liquid passing through the reactor.
  • the known enzyme calorimeters cannot be used for measuring on whole blood as the blood cells will very quickly cause clogging of the column. This problem is reduced a little, but not entirely, as blood has to be diluted at least ten times to obtain a glucose concentration within the range where the column could be expected to respond linearly to the concentration, but this, on the other hand, means that the apparatus should carry a buffer solution sufficient to prepare about 100 samples. As the device according to US 4,021 ,307 works with samples of 1 ml, this means that about 100 ml buffer should be contained in the device for the dilution of the blood alone whereto comes the buffer necessary for rinsing the column after each measurement.
  • the buffer reservoir alone would have a bigger volume than can be permitted for the whole device if it should be given the designation "portable".
  • a sample of 100 ⁇ l whole blood should be provided which is about four times as much as could commonly be obtained by a simple pricking of a finger or an earlobe.
  • Another thing counteracting the use of the enzyme column in a portable apparatus is that the column should be inserted into a thermostatic bath or another kind of thermostate. If the device during the measurement should be maintained at a constant temperature, it will require a preheating period to establish thi temperature before a measuring could be performed, i.e. the measurement canno be made immediately.
  • the preheating and the temperature control will b energy consuming and will call for rather large batteries counteracting the portabilit
  • all these problems are solved if the prejudice of makin a portable device is neglected.
  • Large volumes of buffer are unnecessary if th column is miniaturized.
  • the needed amount of whole blood i reduced, when the flow rate through the column is reduced in accordance with th reduction of the size of the column.
  • the thermostatic bath can b omitted when the column is made sufficiently small. This is due to the fact tha temperature differences in a small device are quickly levelled, the more quickly th smaller the size, so that all parts of the device will have the same temperature.
  • a very small reactor may be obtained if the reactor is constituted by number of parallel channels provided in a substrate and covered by a cover shee bonded to the substrate, the respective ends of the channels being connected to th inlet and the outlet, and the walls of the channels constitute the carrier material o the surface of which an enzyme is immobilized.
  • the substrate may be made fro any material suited for the provision of a microchannel structure by machinery o moulding.
  • the substrate may be a silicon wafer.
  • thermosensors When a silicon wafer is used the thermosensors may appropriately b thermistors integrated on the substrate.
  • the reactor may be surrounded by a tub forming a tight wound helix which tube together with the reactor forms a flow pat for a buffer and for the sample.
  • This arrangement decreases the heat leakage to th surroundings and levels heat gradients which could influence the reactor.
  • Th outside of the enzyme column is insulated with plastic foam.
  • the absolute temperature of the device will be of minor importance.
  • the reaction temperature is not important since excess of enzyme is used leading to conversion of virtually all of the substrate glucose.
  • the temperature response is therefore very little effected by changes in the ambient temperature. Furthermore, this minimizes the need for calibration.
  • the same calibration curve can be used even after considerable loss of enzyme effectivity.
  • the risk of clogging due to the blood cells in the sample is reduced by using as the enzyme carrier a macro porous material having a pore size bigger than 10 ⁇ m.
  • the use of a super porous enzyme carrier has shown to be advantageous, that is a material with pores which penetrates the material completely.
  • a suitable carrier material is agarose.
  • Fig. 1 illustrates schematically the function of an enzyme column for measuring the concentration of a substance in a sample
  • Fig. 2 shows schematically a portable apparatus according to the invention
  • Fig. 3 shows schematically an arrangement of the temperature sensors
  • Fig. 4 shows another arrangement of the temperature sensors
  • Fig. 5 shows schematically a blood dilution and filtration arrangement
  • FIG. 6 illustrates schematically a reactor constituted by channels in a substrate.
  • Figure 1 illustrates schematically the function of an apparatus for measuring the concentration of a substance in a sample which measuring is based on measuring the heat generated by enzymatic oxidation of the substance.
  • a pump 1 forces a buffer through the apparatus at a preset flow rate. At a certain moment the buffer flow is replaced by a sample package which is injected through an injection valve 2.
  • the heat produced by the passage of the sample package through an enzyme column 3 is measured by temperature transducers placed in the inlet and in the outlet of the column, and the signal obtained is sent to an amplifier 4 and is recorded by a recorder 5 at which the temperature difference appears as a peak having a height which is representative of the concentration of the substance in the sample.
  • Figure 2 shows schematically a portable apparatus for measuring the concentration of a substance in whole blood.
  • the apparatus is mainly intended for measuring the glucose concentration in whole blood, but may be used to measure other substances in a body fluid, e.g. alcohol or urea.
  • the buffer pump is provided as a cylinder ampoule 10 having a piston 11 with a piston rod 12 actuated by a pump motor 13 controlled by a microprocessor 14.
  • the pump is controlled to force a buffer 15 through a lead 16, an injection valve 17, a tight wound helix shaped tube 18 surrounding an enzyme column 19, through this enzyme column 19, and through a return lead 20 back to the space above the piston 11 , the cylinder ampoule 10 being closed at its rear end by a closure through which the piston rod 12 may pass sealingly.
  • the turnings of the helix shaped tube 18 are closely adjacent to each other, although in the drawing they are spaced.
  • a sample of whole blood is sucked in through a needle 21 and through the valve 17 which may perform several valve functions.
  • the sample is sucked into another pump 22 which controlled by the microprocessor 14 has been prefilled with a measured amount of the buffer and now still controlled by the microprocessor dilutes a measured amount, e.g. 1 ⁇ l, of the whole blood in the measured amount of buffer, so that the chamber 23 is now filled with a sample of known volume and dilution.
  • the valve 17 is shifted to inject the sample which for some time replaces the buffer flow, but with the same flow rate.
  • the valve 17 shifts back to the buffer flow which forces the sample through the column as a package or plug.
  • the glucose in the sample is decomposed in the presence of the enzyme in the column.
  • This decomposition causes a heating of the sample which heating is measured by the peak difference of the temperatures at the inlet and at the outlet of the column which temperatures are measured by thermistors 24 and 25, respectively, placed in the flow.
  • the microprocessor can calculate with high accuracy the glucose concentration in the whole blood sample and show the result on a display 26.
  • the needle 21 may be designed for pricking through the skin of a patient to directly suck in a sample of body fluid. After use the needle may be ⁇ o retracted into a chamber 27 for disinfection and in all events the needle, also if it is not used for pricking, must be rinsed to avoid that coagulating residual blood clogs the bore of the needle. Spent buffer may be used for the rinsing to economize with the liquid in the apparatus. Parts coming into contact with undiluted blood may further be heparinized to avoid coagulation, is The enzyme column 19 is surrounded by the helix 18 formed by a thin steel tubing. Thereby, a shield is provided protecting the column against outside temperature gradients. Further, the column and the helix are surrounded by an insulating cover 28 made from plastic foam.
  • the liquid will pass through the helix before entering the 2o column.
  • the helix may as well be placed downstream of the column.
  • the thermistors 24 and 25 are shown as placed immediately upstream and downstream, respectively, of the enzyme column. They may, however, both be placed downstream of the column separated by a delay coil 32 sufficiently large to accomodate the sample package as sketched in Fig.3.
  • the thermistor 31 still measures the temperature of the unheated buffer.
  • FIG. 4 is shown another arrangement for differential temperature determination.
  • the flow including that containing the sample, is equally split between two columns, a reference column 42 and an enzyme column 43.
  • a thermistor 40 measures the temperature downstream of the enzyme column 43 and another thermistor 41 measures the reference temperature downstream of the reference column 42.
  • the column is filled with a macro porous material on which enzyme in excess is immobilized. Thereby a good operational stability and low susceptibility to interferences and inhibitors to the enzyme are obtained.
  • the carrier material is chosen to allow diluted whole blood to be used as sample without clogging the column.
  • a special suited material is a super porous agarose gel having pores all way through the particles which pores are big enough for blood cells to pass.
  • An alternative way of increasing the useful life of the column is to remove the blood cells from the sample using a single hollow dialyze fibre as shown in figure 5.
  • the whole blood is led through a fibre 50 having an inlet 51 and an outlet 52.
  • the fibre 50 is surrounded by a space 53 to which the diluting buffer is led through an inlet 54 and removed through an outlet 55.
  • the small molecules of the substance to be measured may pass through the wall of the fibre into the surrounding liquid, but large molecules and cells will be retained. A protection of the column is obtained at the expense of a more complicated diluting procedure.
  • Figure 6 schematically shows a reactor constituted by a number of fine channels 60 provided in a substrate 61.
  • Manifolds 62,63 are provided at the respective ends of the channels 60. These manifolds are also provided in the substrate and are connected to an inlet tube 64 and an outlet tube 65, respectively.
  • the channels 60 are covered by a cover sheet 66 bonded to the substrate 61 by a connective film 67.
  • thermosensors 68 and 69 are bonded to the inlet 64 and outlet 65, respectively.
  • the dimensions of the substrate are typically 14 x 6 x 0.4 mm with a 5 x 1 x 0.014 mm reactor consisting of 33 parallel channels with a total volume of 0.02 ⁇ l.
  • the invention is based on the discovery that the performances, such as signal to noise ratio and sensitivity are virtually unchanged when a conventional enzyme calorimetric device is miniaturized. Differential measurement technique makes it even possible to omit the temperature control when the distances between the measuring and reference temperature sensors and the overall size of the column become sufficiently small. Hereby the construction could be brought to a size making it usable in a really portable device.
  • thermosensors any other kind of sensors may of course be used just as the pumps and valves used may be of any known kind without deviating from the scope of the invention.
  • apparatus may be used with different enzymes for measuring different metabolites such as urea, lactate, ethanol, triglycerides etc.
  • metabolites such as urea, lactate, ethanol, triglycerides etc.
  • hexokinase as well as glucose dehydrogenase can be used besides glucose oxidase.

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  • Chemical & Material Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Combustion & Propulsion (AREA)
  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
  • Pathology (AREA)
  • Investigating Or Analysing Biological Materials (AREA)
  • Apparatus Associated With Microorganisms And Enzymes (AREA)

Abstract

Dispositif portatif servant à mesurer la concentration de glucose dans la totalité d'un échantillon sanguin par la mesure du dégagement de chaleur lorsqu'on provoque la décomposition du glucose en présence d'une enzyme. Le dispositif comporte un calorimètre micro-enzymatique possédant un réacteur (19) doté d'un support superporeux à la surface duquel est immobilisée une enzyme, et des transducteurs thermiques (25, 28) mesurant les températures de l'échantillon avant et après son passage dans le réacteur. Un tube hélicoïdal (18) enroulé de manière serrée et traversé par l'échantillon entoure le réacteur (19) de manière à constituer un blocage thermique. Par ailleurs, le dispositif comporte un réservoir (15) pour un tampon utilisé pour diluer l'échantillon et pour rincer le réacteur après chaque mesure. Un micro-ordinateur (14) règle le passage de l'échantillon et du tampon dans le réacteur (19) et calcule la concentration de glucose à partir de la mesure de la chaleur dégagée.
PCT/DK1992/000213 1991-07-12 1992-07-02 Detecteur portatif de glucose WO1993001489A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP92916171A EP0594773A1 (fr) 1991-07-12 1992-07-02 Detecteur portatif de glucose

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
DK134591A DK134591D0 (da) 1991-07-12 1991-07-12 Baerbart apparat til maaling af koncentrationen af et stof i en legemsvaeske
DK1345/91 1991-07-12
DK1646/91 1991-09-27
DK164691A DK164691D0 (da) 1991-09-27 1991-09-27 Apparat

Publications (1)

Publication Number Publication Date
WO1993001489A1 true WO1993001489A1 (fr) 1993-01-21

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Application Number Title Priority Date Filing Date
PCT/DK1992/000213 WO1993001489A1 (fr) 1991-07-12 1992-07-02 Detecteur portatif de glucose

Country Status (3)

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EP (1) EP0594773A1 (fr)
AU (1) AU2375492A (fr)
WO (1) WO1993001489A1 (fr)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2001057235A2 (fr) * 2000-02-04 2001-08-09 Ciba Specialty Chemicals Water Treatments Limited Analyse de reactions catalysees, par calorimetrie
USRE43316E1 (en) 1997-01-10 2012-04-17 Health Hero Network, Inc. Diabetes management system and method for controlling blood glucose
CN101509888B (zh) * 2009-03-20 2012-06-13 华东师范大学 硅基可集成微型葡萄糖传感器的制作方法
US8262989B2 (en) 2000-07-21 2012-09-11 Senzime Ab (Publ.) Micro-calorimeter apparatus
US8870762B2 (en) 1997-03-28 2014-10-28 Robert Bosch Gmbh Electronic data capture in clinical and pharmaceutical trials
US8945009B2 (en) 2003-05-08 2015-02-03 Robert Bosch Heathcare Systems, Inc. Remote health monitoring system
US9123083B2 (en) 1994-04-26 2015-09-01 Robert Bosch Healthcare Systems, Inc. Blood glucose monitoring system
US9215979B2 (en) 1992-11-17 2015-12-22 Robert Bosch Healthcare Systems, Inc. Multi-user remote health monitoring system
US9477939B2 (en) 1992-11-17 2016-10-25 Robert Bosch Healthcare Systems, Inc. Radio frequency based remote health monitoring
WO2017184650A3 (fr) * 2016-04-19 2017-12-14 Malvern Instruments Incorporated Procédé et appareil de calorimétrie différentielle à balayage

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3839798A1 (de) * 1988-11-25 1990-06-07 Eppendorf Geraetebau Netheler Reaktionswaermeenzymkalorimeter
US4935345A (en) * 1987-04-07 1990-06-19 Arizona Board Of Regents Implantable microelectronic biochemical sensor incorporating thin film thermopile
US5017494A (en) * 1986-04-02 1991-05-21 Seiko Instruments & Electronics Ltd. Bio-thermo tip sensor

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5017494A (en) * 1986-04-02 1991-05-21 Seiko Instruments & Electronics Ltd. Bio-thermo tip sensor
US4935345A (en) * 1987-04-07 1990-06-19 Arizona Board Of Regents Implantable microelectronic biochemical sensor incorporating thin film thermopile
DE3839798A1 (de) * 1988-11-25 1990-06-07 Eppendorf Geraetebau Netheler Reaktionswaermeenzymkalorimeter

Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9215979B2 (en) 1992-11-17 2015-12-22 Robert Bosch Healthcare Systems, Inc. Multi-user remote health monitoring system
US9477939B2 (en) 1992-11-17 2016-10-25 Robert Bosch Healthcare Systems, Inc. Radio frequency based remote health monitoring
US9123083B2 (en) 1994-04-26 2015-09-01 Robert Bosch Healthcare Systems, Inc. Blood glucose monitoring system
USRE43316E1 (en) 1997-01-10 2012-04-17 Health Hero Network, Inc. Diabetes management system and method for controlling blood glucose
US8870762B2 (en) 1997-03-28 2014-10-28 Robert Bosch Gmbh Electronic data capture in clinical and pharmaceutical trials
US8990336B2 (en) 1997-03-28 2015-03-24 Robert Bosch Healthcare Systems, Inc. Networked system for interactive communication and remote monitoring of individuals
WO2001057235A3 (fr) * 2000-02-04 2002-04-25 Ciba Spec Chem Water Treat Ltd Analyse de reactions catalysees, par calorimetrie
WO2001057235A2 (fr) * 2000-02-04 2001-08-09 Ciba Specialty Chemicals Water Treatments Limited Analyse de reactions catalysees, par calorimetrie
US8262989B2 (en) 2000-07-21 2012-09-11 Senzime Ab (Publ.) Micro-calorimeter apparatus
US8945009B2 (en) 2003-05-08 2015-02-03 Robert Bosch Heathcare Systems, Inc. Remote health monitoring system
CN101509888B (zh) * 2009-03-20 2012-06-13 华东师范大学 硅基可集成微型葡萄糖传感器的制作方法
WO2017184650A3 (fr) * 2016-04-19 2017-12-14 Malvern Instruments Incorporated Procédé et appareil de calorimétrie différentielle à balayage
US10386315B2 (en) 2016-04-19 2019-08-20 Malvern Panalytical Inc. Differential scanning calorimetry method and apparatus

Also Published As

Publication number Publication date
AU2375492A (en) 1993-02-11
EP0594773A1 (fr) 1994-05-04

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