WO2006076930A1 - Dispositif de surveillance en continu du glucose - Google Patents

Dispositif de surveillance en continu du glucose Download PDF

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Publication number
WO2006076930A1
WO2006076930A1 PCT/EP2005/000566 EP2005000566W WO2006076930A1 WO 2006076930 A1 WO2006076930 A1 WO 2006076930A1 EP 2005000566 W EP2005000566 W EP 2005000566W WO 2006076930 A1 WO2006076930 A1 WO 2006076930A1
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WO
WIPO (PCT)
Prior art keywords
fluid
analyte
probe
microdialysis
concentration
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Application number
PCT/EP2005/000566
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English (en)
Inventor
Hans-Peter Haar
George Bevan Kirby Meacham
Hans List
Herbert Harttig
Felix Baader
Original Assignee
Roche Diagnostics Gmbh
F.Hoffmann-La Roche Ag
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.)
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Publication date
Application filed by Roche Diagnostics Gmbh, F.Hoffmann-La Roche Ag filed Critical Roche Diagnostics Gmbh
Priority to PCT/EP2005/000566 priority Critical patent/WO2006076930A1/fr
Publication of WO2006076930A1 publication Critical patent/WO2006076930A1/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, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14525—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using microdialysis
    • 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, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement

Definitions

  • This invention generally relates to devices for sensing a concentration of chemical constituents in body fluid such as interstitial fluid, including but not limited to glucose.
  • the devices also relates to systems for measuring and reporting the concentration of body fluid constituents at time intervals shorter than the physiological response time, thereby providing effectively continuous concentration measurements.
  • Metabolic processes of living organisms depend on maintaining the concentration of chemical compounds, including glucose, within certain limits in the interstitial fluid surrounding living cells. This fluid occupies perhaps 20% of the tissue volume, and cells take up the balance of the volume. The fluid actively flows through the tissue and the flow source is plasma filtered through the arterial capillary walls and leaked through the venous capillaries, and the sink flows into the venous capillaries and the lymphatic system.
  • chemical compounds including glucose
  • the flow rate is reported to be approximately 0.36*10 ⁇ 2 ml/sec*ml of tissue, and results in a complete change of fluid in each milliliter of tissue in less than 5 minutes.
  • the cells absorb required materials, including oxygen and glucose, from this flowing fluid.
  • waste products, including carbon dioxide are released into the fluid.
  • This flow provides one mechanism for bringing oxygen and glucose to the cells. Diffusion of oxygen and glucose, both small molecules, provides a second transfer mechanism. As a result of these transfer mechanisms, the concentration of glucose in the interstitial fluid is very nearly the same as in the arterial capillaries.
  • interstitial fluid does not contain blood cells and it does not clot.
  • the static pressure of the interstitial fluid is at or below atmospheric pressure, while the capillary blood pressure is on the order of 30 mmHg above atmospheric interstitial fluid.
  • the interstitial fluid protein content is lower than that of the blood plasma, and creates an inward osmotic pressure across the capillary walls. This inward osmotic pressure is an important component of the overall pressure and flow balance between the capillaries and the tissue.
  • living organisms employ homeostatic mechanisms to control the concentration of glucose and other constituents in the blood and interstitial fluid, since concentrations outside
  • living organisms employ homeostatic mechanisms to control the concentration of glucose and other constituents in the blood and interstitial fluid, since concentrations outside these limits may cause pathology or death.
  • specialized pancreatic cells sense blood glucose levels, and release insulin as glucose increases. Insulin receptors in other tissues are activated, and increase glucose metabolism to reduce the glucose level.
  • Type I diabetes is caused by death of insulin producing cells
  • Type II diabetes is caused by reduced insulin receptor sensitivity. In both cases, the result is excess blood glucose.
  • the blood glucose may be controlled, particularly in the case of type I diabetes, by administration of insulin. While this is effective in reducing glucose, the dose must quantitatively be matched to the amount of glucose reduction required. An insulin overdose may lead to very low blood glucose, and result in coma or death.
  • glucose level For diabetic patients control of glucose level is a difficult regimen.
  • the established method of glucose measurement uses small samples of blood obtained from arterial capillaries by pricking the finger and expressing the sample onto a disposable test strip. A meter device is used to read the test strip and report a quantitative blood glucose concentration. The appropriate dose of insulin is then calculated, measured out, and administered with a hypodermic needle.
  • the overall process is both painful and technically demanding, and cannot be sustained by many diabetic patients.
  • Automated insulin delivery devices have been developed that help some patients maintain the regimen., thereby their glucose level. These devices are small, wearable devices that contain a reservoir of insulin, an insulin pump, a programmable control and a power source. Insulin is delivered to the subcutaneous tissue on a programmed dosage schedule through a catheter implanted in the subcutaneous tissue. The schedule is set to provide the approximate baseload requirements of the particular patient. The patient then makes periodic blood glucose measurements and adjusts the dosage to correct his glucose level. The catheter remains in the subcutaneous tissue for a day or two, after which it is replaced by a new catheter in a different location. This periodic catheter change is needed to prevent tissue reactions that encapsulate the catheter, and to minimize the chance of infection where the catheter passes through the skin. While this reduces or eliminates hypodermic injections, frequent finger pricking and test strip measurements are still required.
  • Noninvasive optical or chemical devices provide relative measurements at best, and have not proven capable of providing an absolute measurement that is reliable enough to determine the insulin dose.
  • Trancutaneous or totally implanted glucose probes based on electrochemical or spectroscopic principles provide absolute measurements of the interstitial fluid glucose. This measurement tracks blood glucose, and may be used as a basis for insulin administration. The problem is probe encapsulation as well as aging of the employed sensors that degrades the measurement in a matter of a few days.
  • Interstitial fluid is an attractive target for continuous glucose measurement. It floods the subcutaneous tissue, and is readily accessed through a small, relatively painless penetration of the upper dermis layers. Further, interstitial fluid's freedom from clotting allows a single penetration to be used for a period of hours to days. It also facilitates sample transport through small tubes in measurement devices. Blood in subcutaneous tissue is a less attractive target for continuous glucose measurement. Capillaries must be cut to gain access to the blood, and this starts a process of clotting and healing that stops the flow in a matter of minutes. Further, blood will clot in small tubes unless anticoagulant chemicals are added.
  • US 4,777,953 partially discloses real-time measurement of interstitial tissue glucose concentrations. It shows the use of implanted microporous tubular membranes to collect an ultrafiltrate of blood or interstitial fluid. A vacuum applied to the lumens of the implanted tubes draws liquid through the porous tube wall that includes low molecular weight molecules such as glucose, and excludes high molecular weight molecules such as proteins. AU the fluid comes from the patient's body, and no additional fluid is used. Ultrafiltration systems therefore suffer from the same drawbacks as the systems described in WO 02/62210 and WO 00/22977.
  • the system employs single use test zones for measuring the glucose level.
  • test zones can operate with smaller samples and the implantable probes consequently can be smaller and less invasive.
  • a system to expose perfusion fluid to body fluid through an implantable tubular microdialysis probe is disclosed.
  • Diffusion of small analyte molecules such as glucose through the tube wall causes the analyte concentrations in the perfusion fluid to equilibrate with the concentrations in the body fluid.
  • this dialysate is sampled at specified time intervals and deposed on a new single-use test element wherein the analyte is measured.
  • test elements maybe e.g. test zones on a tape. After the measurement, the used single-use test element and dialysate sample are moved from the measuring area to a waste storage area.
  • Another aspect of the invention is to reduce the physiological effects of the sample withdrawal process.
  • the glucose concentration in the interstitial fluid immediately adjacent to the probe is slightly depressed, and this depleted fluid is constantly replaced by the relatively large flow rate through the tissue surrounding the catheter. This minimizes the effect of the glucose withdrawal on the flow rate and chemical composition of the interstitial fluid, and provides a long time over which concentration monitoring can be made at the same implantation site.
  • in the microdialysis process disclosed there is virtually no net volume of body fluid withdrawn. Therefore, the body is not depleted of fluid and hence measurement can prolong for a long time.
  • pump means are disclosed which are advantageous for withdrawing minute amounts of dialysate fluid from an implanted microdialysis probe, and for replenishing the dialysate in the probe with fluid.
  • single use test elements allows dialysate analyte concentration to be measured on demand, rather than as a continuous measurement of a constant flow stream. This facilitates measurement of analyte concentration in the dialysate for different equilibration times. Such measurements can, for example, distinguish changes in the analyte concentration in the body fluid from changes in the membrane and their associated diffusion behavior. This capability enables self-diagnostic and self- calibration functions that are not possible with a continuous flow measurement device such as an electrochemical cell, and increases the robustness of the measurement.
  • the system has a control unit which controls the transport of test zones and reading of test zones in a timely coordinated manner.
  • the control unit further may control a pump means to discharge fluid containing analyte from the microdialysis or microperfusion probe onto test zones.
  • Particularly useful control cycles have been found which reduce timelags caused by discharging fluid onto test zones which haven't been in exchange with body fluid for some time.
  • fluid contained in a space between a region of exchange with body fluid and the discharge opening is expelled shortly before discharging fluid onto a fresh test zone.
  • a discharge of "old" fluid which hasn't actually equilibrated with body fluid can be discharged onto a test zone which already had been used for analysis previously.
  • a circulation of fluid in the probe may be employed to avoid fluid with an old information of body analyte concentration to be discharged onto a fresh test zone.
  • Figures 1, 2 and 3 show a series of views illustrating the functional elements and operation of a first system for microdialysis based continuous monitoring of interstitial fluid composition operating in a first unidirectional flow mode;
  • Figures 4, 5 and 6 show a series of views illustrating the functional elements and operation of a first system for microdialysis based continuous monitoring of interstitial fluid composition operating in a second unidirectional flow mode;
  • Figures 7, 8 and 9 show a series of views illustrating the functional elements and operation of a first system for microdialysis based continuous monitoring of interstitial fluid composition operating in a bidirectional flow mode;
  • Fig. 10 shows a segment of a testing tape with multiple test zones
  • Figures 11, 12 and 13 show a series of views illustrating the functional elements and operation of a second system for microdialysis based continuous monitoring of interstitial fluid composition
  • Fig. 14 shows a microdialysis loop-flow probe optimized for minimally invasive tissue insertion.
  • Figure. 1 schematically shows a first system embodiment operating in a first unidirectional flow mode and combining an implanted microdialysis probe sample collection means with a testing tape analyte measuring means.
  • a tubular microdialysis membrane probe 1 is inserted in the subcutaneous tissue 2 such that the fluid 3 may be passed through the probe 1. This establishes a diffusion path through the membrane between the fluid and the interstitial fluid.
  • Fresh fluid is supplied to the microdialysis probe inlet by a piston 4 and cylinder 5.
  • the piston 4 may be driven by a stepper motor, servo, or similar mechanism (not shown) under system control, and the cylinder forms the fluid reservoir.
  • the microdialysis probe outlet is connected to a transfer tube 6 that leads to a sample discharge opening 7.
  • the microdialysis probe 1 is shown in the schematic illustration as a U shaped member penetrating the skin twice for clarity. In practice, a folded or coaxial arrangement requiring only a single penetration is preferred.
  • the sample discharge opening 7 is close to and aligned with the optical port 8 of reader unit 9.
  • a translucent testing tape 10 with multiple hydrophilic test zones on the outer surface 11 passes through the gap between sample discharge opening 7 and optical port 8.
  • Figure. 10 shows multiple hydrophilic test zones 12 on a segment of testing tape 10. Unused testing tape on storage reel 13 is led around reader unit 9 to waste reel 14. Prior to each measurement, the testing tape 10 is advanced such that an unused test zone is positioned directly between optical port 8 and sample discharge opening 7 by a tape drive mechanism (not shown) under system control.
  • a system control module (not shown) integrates the mechanical, optical, sensing and data processing functions to make a time sequence of measurements and transmit the results to the patient and health care professionals.
  • Figures 1 through 3 together show the operating cycle that provides an analyte concentration measurement using the first unidirectional flow mode.
  • Figure. 1 shows the starting position.
  • the microdialysis probe 1 and transfer tube 6 are filled with the perfusion fluid 3.
  • the perfusion fluid 3 within microdialysis probe 1 exchanges substances with the surrounding interstitial fluid and thereby equilibrates with the interstitial fluid in tissue 2 to form dialysate.
  • a typical equilibration time is 0.5 to 5 minutes.
  • the fluid volume in transfer tube 6 does not communicate with the interstitial fluid, and therefor retains the concentration values it reached while it was in microdialysis probe 1 during the previous cycle.
  • This portion of the dialysate has a volume of e.g.
  • FIG. 2 shows the measurement process.
  • Piston 4 is pushed into cylinder 5 to displace fluid 3 through microdialysis probe 1 and transfer tube 6.
  • a small amount, e.g. 10 to 50 nanoliters, of dialysate 3 leaves discharge opening 7.
  • This action forms dialysate droplet 17 in the gap between discharge opening 7 and testing tape 10.
  • This droplet has a small volume, e.g. 10 to 50 nanoliters. The dimensions are adjusted so that dialysate droplet 17 contacts a hydrophilic test zone 12 on testing tape 7.
  • dialysate droplet 17 is drawn onto hydrophilic test zone 12 where it forms a wet spot and initiates a color change reaction.
  • Reader unit 9 illuminates the wet spot on test zone 12 through translucent testing tape 10 using optical port 8. The intensity and spectrum of light reflected back into optical port 8 is a function of the color change, and therefore of the analyte concentration in the dialysate sample droplet 17.
  • Reader unit 9 detects the intensity and spectrum of the reflected light, and transmits this information to the system control module where the concentration is calculated and added to the time sequence of measurements. These analyte values are reported, and may be used to guide therapy. Each measuring operation requires some seconds, a short period relative to the interval between measurements.
  • Figure 3 shows the reset operation to prepare for the next measurement.
  • new fluid 3 equilibrates with the interstitial fluid in subcutaneous tissue 2 preparatory to making the next measurement about 0,5 to 5 minutes later.
  • the testing tape 10 is advanced to bring the next test field 12 into alignment between optical port 8 and sample discharge opening 7.
  • piston 4 is not in the starting position shown in Fig. 1, since the dispensed dialysate is replaced by fresh perfusion fluid from cylinder 5.
  • the measured analyte concentration lags the actual interstitial fluid concentration by the cycle period, e.g. 0.5 to 5 minutes, since the fluid comprising the measured dialysate droplet was equilibrated in the previous cycle.
  • FIGS 4 through 6 together show the operating cycle that provides an analyte concentration measurement using the second unidirectional flow mode.
  • the system configuration is the same as described relative to Figure. 1, and is not repeated.
  • FIG. 4 shows the starting position.
  • the microdialysis probe 1 and transfer tube 6 are filled with perfusion fluid 3.
  • the perfusion fluid within microdialysis probe 1 equilibrates with the interstitial fluid in tissue 2.
  • a typical equilibration time is e.g. 0.5 to 5 minutes.
  • the dialysate in transfer tube 6 does not communicate with the interstitial fluid, and therefor retains the concentration values it reached while it was in microdialysis probe 1 during the previous cycle.
  • This portion of the dialysate has a volume of e.g. 20 nanoliters where transfer tube 6 has an inside diameter of 20 microns and a length of 10 millimeters.
  • Figure 5 shows the first part of the measuring process. Piston 4 is pushed into cylinder 5 to displace perfusion fluid 3 through microdialysis probe 1. The fluid volume in transfer tube 6 is deposited on used test field 12 as waste droplet 18, and thereby purged from the system. Piston 5 then stops.
  • Fig. 6 shows the second part of the measuring process. New measuring field 12 is moved into position opposite discharge opening 7, in the process moving the used test field that contains the purged dialysate toward waste reel 14. Piston 4 is then pushed into cylinder 5 to displace perfusion fluid 3 through microdialysis probe 1 and transfer tube 6. A small amount, e.g.
  • dialysate droplet 17 has a small volume, e.g. 10 to 50 nanoliters. The dimensions are adjusted so that dialysate droplet 17 contacts new hydrophilic test zone 12 on testing tape 7. At least a portion of dialysate droplet 17 is drawn onto hydrophilic test zone 12 where it forms a wet spot and initiates a color change reaction. The color change is measured and interpreted as in the description of Figures 1 through 3.
  • Figures 7 through 9 together show the operating cycle that provides an analyte concentration measurement using the bidirectional flow mode. Again, the system configuration is the same as described relative to Figure. 1, and is not repeated.
  • Figure 7 shows the starting position.
  • the microdialysis probe 1 is partially filled with perfusion fluid 3, and partly with air 15 drawn in from the discharge opening 7, with a meniscus 16 separating the air from the liquid. This allows perfusion fluid 3 within microdialysis probe 1 to equilibrate with the interstitial fluid in tissue 2 and form dialysate.
  • a typical equilibration time is e.g. 0.5 to 5 minutes.
  • Figure 8 shows the measurement process.
  • Piston 4 is pushed into cylinder 5 to displace fluid 3 through microdialysis probe 1 and transfer tube 6 such that all of the air 15 and a small amount of dialysate 3 leaves discharge opening 7.
  • This action forms dialysate droplet 17 in the gap between discharge opening 7 and testing tape 10.
  • This droplet has a small volume, e.g. 10 to 50 nan outers.
  • the dimensions are adjusted so that dialysate droplet 17 contacts hydrophilic test zone 12 on testing tape 7. At least a portion of dialysate droplet 17 is drawn onto hydrophilic test zone 12 where it forms a wet spot and initiates a color change reaction. The color change is measured and interpreted as in the description of Figures 1 through 3.
  • Figure 9 shows the reset operation to prepare for the next measurement.
  • Piston 4 is pulled out of cylinder 5 to withdraw perfusion fluid 3 and draw in air 15 so that meniscus 16 is restored to its original position.
  • perfusion fluid 3 can again equilibrate with the interstitial fluid in subcutaneous tissue 2 preparatory to making the next measurement e.g. 0,5 to 5 minutes later.
  • the testing tape 10 is advanced to bring the next test field 12 into alignment between optical port 8 and sample discharge opening 7.
  • piston 4 is not in the starting position shown in Fig. 7, since the dispensed dialysate is replaced by fresh perfusion fluid from cylinder 5.
  • the measured analyte concentration has minimum time lag relative to the actual interstitial fluid concentration, since the fluid comprising the measured dialysate droplet was equilibrated in the current cycle.
  • FIG 11 schematically shows a second system embodiment combining an implanted microdialysis probe sample collection means with a testing tape analyte measuring means.
  • a tubular microdialysis membrane probe 1 is inserted in the subcutaneous tissue 2 such that perfusion fluid 3 may be passed through the probe and re-circulated to the inlet 20.
  • a pump 21 circulates perfusion fluid 3 at a relatively high rate, e.g. one or two cycles per minute. This allows the circulating perfusion fluid 3 in the loop to equilibrate with the interstitial fluid in tissue 2 through diffusion membrane 1. Fresh perfusion fluid is supplied to the flow loop through inlet 20 by piston 4 and cylinder 5.
  • the piston may be driven by a stepper motor, servo, or similar mechanism (not shown) under system control, and the cylinder forms the perfusion fluid reservoir.
  • the circulating perfusion fluid loop outlet 22 is connected to transfer tube 6 that leads to sample discharge opening 7.
  • the sample discharge opening 7 is close to and aligned with the optical port 8 of reader unit 9.
  • the tape measurement subsystem configuration and the overall system controls are similar to those described relative to Fig. 1.
  • microdialysis probe 1 is shown as a U shaped member penetrating the skin twice, while in practice a folded or coaxial arrangement requiring only a single penetration is preferred.
  • FIGs 11 through 13 together show the operating cycle that provides an analyte concentration measurement using the second system embodiment. It is illustrated using the bidirectional flow mode described relative to Figures 7 through 9, but is equally adapted to the unidirectional flow modes described relative to Figures 1 through 3 and Figures 4 through 6.
  • Figure 11 shows the starting position.
  • the circulating loop of perfusion fluid 3 is completely filled, and circulation is maintained by pump 21.
  • Transfer tube 6 is partly filled with air 15 drawn in from discharge opening 7, with meniscus 16 separating the air from the liquid.
  • the entire volume of perfusion fluid 3 within the flow loop passes through microdialysis probe 1 multiple times, and equilibrates with the interstitial fluid in tissue 2 to form dialysate.
  • a typical equilibration time is e.g. 0.5 to 5 minutes.
  • Figure 12 shows the measurement process.
  • Piston 4 is pushed into cylinder 5 to displace perfusion fluid 3 into inlet 20.
  • This action displaces dialysate out through outlet 22 and into transfer tube 6 such that all of the air 15 and a small amount of dialysate 3 leaves discharge opening 7.
  • This action forms dialysate droplet 17 in the gap between discharge opening 7 and testing tape 10.
  • This droplet has a small volume, e.g. 10 to 50 nanoliters.
  • the dimensions are adjusted so that dialysate droplet 17 contacts hydrophilic test zone 12 on testing tape 7.
  • At least a portion of dialysate droplet 17 is drawn onto hydrophilic test zone 12 where it forms a wet spot and initiates a color change reaction. This operation requires only a few seconds. The color change is measured and interpreted as in the description of Figures 1 through 3.
  • Figure 13 shows the reset operation to prepare for the next measurement.
  • piston 4 is pulled out of cylinder 5 to withdraw perfusion fluid 3 and draw in air 15 so that meniscus 16 is restored to its original position.
  • the reset operation also requires only a few seconds, and perfusion fluid 3 in the flow loop continues to equilibrate with the interstitial fluid in subcutaneous tissue 2 preparatory to making the next measurement, e.g. 0,5 to 5 minutes later.
  • the testing tape 10 is advanced to bring the next test field 12 into alignment between optical port 8 and sample discharge opening 7. It should be noted that piston 4 is not in the starting position shown in Figure 11, since the dispensed dialysate is replaced by fresh perfusion fluid from cylinder 5.
  • the measured analyte concentration has minimum time lag relative to the actual interstitial fluid concentration, since the fluid comprising the measured dialysate droplet was equilibrated in the current cycle.
  • the advantages of this system include mixing that enhances the diffusion rate of glucose for a given microdialysis membrane area.
  • FIG.4 shows a tubular microdialysis membrane probe 30 that incorporates loop flow and is inserted into the subcutaneous tissue through a single small opening in the skin.
  • Microdialysis membrane tube 31 has a fluid input end 33 and a fluid output end 34 positioned at the proximal probe end 39.
  • the tube 31 is formed into a loop and wound with multiple turns around a support wire core 32, such that the spiral windings 35 extend from the proximal probe end 39 to the distal probe end 37.
  • the fluid input and output legs of the loop form nested spirals, and are connected by an integral return bend 36 at the distal probe tip 37.
  • Probe 30 may be small, e.g. 0.5 millimeters diameter and an insertion depth of 15 millimeters, constructed of 0.15 millimeter outside diameter microdialysis membrane tubing 31 and a 0.15 millimeter diameter wire core 32.
  • the construction is flexible, providing less discomfort that a rigid probe that does not conform with body movements.
  • Single use test elements exemplified by testing tape 7 with hydrophilic test zones 12 permit measurement of dialysate analyte absolute concentration on demand at any time. Measurement of the concentration after a sequence of different equilibration time periods (e.g. 0,2, 0,5, 1, 2, and 5 minutes) equilibrium time is an aspect of this invention. These measured concentration values allow calculation of an effective membrane diffusion constant (k) independent of the absolute concentration values. A change in diffusion constant k indicates a change in the microdialysis membrane 1 or its interface with the interstitial fluid in tissue 2. This capability enables self-diagnostic and self-calibration functions. Excessive change in k, for example, may be used to trigger an alarm that warns the user of a possible malfunction.
  • k membrane diffusion constant
  • Determination of k also allows extrapolation of measurements made with short equilibration times to fully equilibrated concentrations without a separate verification measurement.
  • Equilibration times may be varied for each measurement, providing a continuous update of the response behavior of the diffusion process.
  • a special sequence of equilibration times may be run periodically, e.g. every 30 minutes, to determine the response behavior of the diffusion process.
  • continuous flow measurement devices such as electrochemical cells cannot distinguish changes in the analyte concentration in the body fluid from changes in the microdialysis membrane performance, and require a separate verification measurement to determine the fully equilibrated concentration. Measurement on demand, therefore, provides a unique means of validating the concentration measurements and providing built-in means for quality control and robust results.
  • Colormetric measurement using a testing tape analyte measuring means has a further advantage compared to electrochemical cell measuring devices.
  • Dialysate droplet 17 leaves discharge opening 7 and transfers across a gap to testing tape 10.
  • the entire "dry" subassembly containing testing tape 10 and reader unit 9 may therefore be easily separated from the "wet" subassembly containing microdialysis membrane probe 1, piston 4, cylinder 5, transfer tube 6 and sample discharge opening 7.
  • This allows the "wet” subassembly to be sterilized to allow tissue contact, and the "dry” subassembly that does not contact tissue to be non-sterile. This is important because the test chemistry often deteriorates during sterilisation.
  • Flow-through electrochemical cell in contrast, are by necessity part of the "wet" subassembly, and must be sterilized. This is a demanding operation that increases production cost and complexity.
  • the spot size on the test zone can be correlated to the sample volume.
  • the optical module has the additional function of measuring the spot size to assure adequate liquid for a reliable measurement.
  • the spot size measurement provides feedback information to the piston drive so that the spot size is actively controlled.
  • Physical fluid interchange between the interstitial fluid and the dialysate may be detected through measurement of a second marker parameter in dialysate droplet 17.
  • the marker measurement may be an additional function of test zone 12 on testing tape 7, or a separate measurement (not shown).
  • the invention includes measurement of a second marker parameter to detect such interchange, and correction of the glucose measurement in the dialysate to reflect the interstitial fluid glucose concentration more accurately.
  • the marker may be an endogenous parameter in the interstitial fluid or an exogenous parameter in the fluid.
  • test strips suitable for use in the present invention are for example described in US 6,039,919.
  • the strips have a test zone that is impregnated with a reagent system so that the color of the zone is changed based on reaction with the analyte to be determined.
  • Such test zones advantageously can be provided on a tape rather than providing each test zone on an individual carrier.
  • Such embodiments allow convenient transport of fresh test zones into a contact zone where liquid sample is then applied to the test zone.
  • the color change caused by the analyte is measured optically by a reader unit that produces signals that are a function of the concentration of the analyte.
  • the signals are processed in a processing unit to calculate the concentration of the analyate.
  • the optical measuring system may be used to determine the actual sample volume delivered to the test zone as a feedback signal to control the pumping means.
  • Such an optical measuring system can be provided by a CCD chip onto which an image of the test zone is projected. Evaluation of the image shows the area wetted by sample liquid and determines the amount of sample fluid received on the test zone.

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Abstract

De manière générale, la présente invention concerne des dispositifs de détection d'une concentration de constituants chimiques, tel que le glucose, entre autres, dans du fluide corporel tel que le fluide interstitiel. Les dispositifs comprennent également des systèmes de mesure et d'établissement de rapport portant sur la concentration des constituants de fluide corporel sur des intervalles de temps plus courts que le temps de réponse physiologique, ce qui produit ainsi des mesures de la concentration effectivement continues. Le dispositif selon l'invention comprend une sonde, un réservoir contenant du fluide de perfusion relié à une entrée de la sonde, au moins une zone d'essai qui comprend un réactif prévu pour réagir avec l'analyte afin de produire un changement décelable, une unité de lecture qui lit les zones d'essai mouillées avec le fluide contenant l'analyte, ladite unité de lecture produisant des signaux correspondant à la concentration de l'analyte présent dans le fluide; et une unité de traitement qui traite les signaux et la concentration de l'analyte.
PCT/EP2005/000566 2005-01-21 2005-01-21 Dispositif de surveillance en continu du glucose WO2006076930A1 (fr)

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3101571A1 (fr) 2015-06-03 2016-12-07 Roche Diabetes Care GmbH Système de mesure pour mesurer la concentration d'un analyte avec un capteur d'analyte sous-cutané
EP3226161A1 (fr) 2016-03-31 2017-10-04 Roche Diabetes Care GmbH Instrument permettant de surveiller la concentration d'un analyte

Citations (3)

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EP3101571A1 (fr) 2015-06-03 2016-12-07 Roche Diabetes Care GmbH Système de mesure pour mesurer la concentration d'un analyte avec un capteur d'analyte sous-cutané
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