WO2012132432A1 - 生体試料測定装置 - Google Patents
生体試料測定装置 Download PDFInfo
- Publication number
- WO2012132432A1 WO2012132432A1 PCT/JP2012/002155 JP2012002155W WO2012132432A1 WO 2012132432 A1 WO2012132432 A1 WO 2012132432A1 JP 2012002155 W JP2012002155 W JP 2012002155W WO 2012132432 A1 WO2012132432 A1 WO 2012132432A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- sensor
- biological sample
- measurement
- acceleration
- acceleration sensor
- Prior art date
Links
Images
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
- G01N27/30—Electrodes, e.g. test electrodes; Half-cells
- G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
-
- 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/15—Devices for taking samples of blood
- A61B5/150007—Details
- A61B5/150015—Source of blood
- A61B5/150022—Source of blood for capillary blood or interstitial fluid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/15—Devices for taking samples of blood
- A61B5/150007—Details
- A61B5/150358—Strips for collecting blood, e.g. absorbent
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/15—Devices for taking samples of blood
- A61B5/151—Devices specially adapted for taking samples of capillary blood, e.g. by lancets, needles or blades
- A61B5/15101—Details
- A61B5/15126—Means for controlling the lancing movement, e.g. 2D- or 3D-shaped elements, tooth-shaped elements or sliding guides
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/15—Devices for taking samples of blood
- A61B5/157—Devices characterised by integrated means for measuring characteristics of blood
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/4875—Details of handling test elements, e.g. dispensing or storage, not specific to a particular test method
-
- C—CHEMISTRY; METALLURGY
- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
- C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
- C12Q1/001—Enzyme electrodes
- C12Q1/005—Enzyme electrodes involving specific analytes or enzymes
- C12Q1/006—Enzyme electrodes involving specific analytes or enzymes for glucose
-
- C—CHEMISTRY; METALLURGY
- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
- C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
- C12Q1/54—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving glucose or galactose
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N2333/00—Assays involving biological materials from specific organisms or of a specific nature
- G01N2333/90—Enzymes; Proenzymes
- G01N2333/902—Oxidoreductases (1.)
- G01N2333/904—Oxidoreductases (1.) acting on CHOH groups as donors, e.g. glucose oxidase, lactate dehydrogenase (1.1)
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/64—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving ketones
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/66—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood sugars, e.g. galactose
Definitions
- the present invention relates to a biological sample measuring device, for example, a biological sample measuring device for measuring a blood glucose level.
- the configuration of the conventional biological sample measurement device includes a main body case having a sensor insertion portion, a measurement portion connected to the sensor insertion portion, a control portion connected to the measurement portion, and a display connected to the control portion. (See, for example, Patent Document 1).
- the blood glucose level is measured by the measurement portion, and the measured blood glucose level is displayed on the display portion.
- the problem with the conventional biological sample measuring device is that the measurement accuracy may be low. That is, in the conventional biological sample measuring apparatus, when blood is spotted on the blood glucose level sensor inserted in the sensor insertion portion, the blood reaches the reaction reagent and an electrochemical reaction occurs. And a blood glucose level is detected by measuring the state of this electrochemical reaction with a measurement part. However, if an impact is applied to the blood glucose level sensor after the blood is spotted on the blood glucose level sensor and the measurement is completed, the blood does not smoothly reach the reagent part, resulting in measurement accuracy. May decrease.
- an object of the present invention is to improve the measurement accuracy of the biological sample measurement device.
- the present invention provides a body case having a sensor insertion portion, a measurement portion connected to the sensor insertion portion, a control portion connected to the measurement portion, and a control portion connected to the control portion.
- a biological sample measuring device provided with an acceleration sensor that includes a display unit and detects an impact applied to the sensor insertion unit.
- the acceleration sensor is preferably disposed in the sensor insertion portion. This achieves the intended purpose.
- the measurement accuracy can be improved. That is, in the present invention, for example, when an impact is applied to the sensor insertion part via a biological sample measurement sensor that measures a blood sugar level or the like, the acceleration sensor detects the impact. If the impact exceeds a predetermined value, the measurement result measured by the measurement unit can be displayed on the display unit as inappropriate. Therefore, inappropriate measurement values are not displayed and measurement accuracy can be improved.
- Embodiment 1 Sectional view of the biological sample measuring apparatus shown in FIG. Plan view of the biological sample measuring apparatus shown in FIG. Control block diagram of the biological sample measuring apparatus shown in FIG. Measurement flow chart of the biological sample measuring device shown in FIG.
- the figure which shows the example of the error display of the biological sample measuring apparatus shown by FIG. Plan view of biological sample measurement apparatus according to Embodiment 2 Plan view of biological sample measuring apparatus according to Embodiment 3 Plan view of biological sample measuring apparatus according to Embodiment 4 Control block diagram of the biological sample measuring apparatus shown in FIG. Internal sectional view of biological sample measuring apparatus according to Embodiment 5 The figure which shows the relationship between each axis
- Diagram showing vector component of measurement acceleration The figure which shows an example of the waveform of the output signal of an acceleration sensor
- the figure which shows another example of the output waveform of an acceleration sensor The graph which shows the waveform pattern of the applied voltage for performing a blood glucose level measurement in the biological sample measuring device in Embodiment 6.
- Plan view of biological sample measuring apparatus according to Embodiment 7 In the biological sample measurement apparatus in the eighth embodiment, a measurement operation flowchart including additional spotting
- FIG. 1 is a perspective view of the biological sample measuring apparatus of the present embodiment
- FIG. 2 is a sectional view thereof
- FIG. 3 is a top view thereof
- FIG. 4 is a control block diagram thereof.
- the biological sample measurement device of the present embodiment includes a main body case 2 having a sensor insertion portion 1 at one end thereof.
- the sensor insertion part 1 is configured so that a sensor 11 having a spotting part 11a can be inserted.
- the display unit 3 and the operation buttons 14 and 15 are provided on the upper surface of the main body case 2.
- the sensor insertion part 1 is arrange
- a connector part (not shown) that is electrically connected to the biological sample measurement sensor 11 to be inserted is provided inside the sensor insertion part 1.
- the measurement unit configured on the substrate 4 and the connection part of the biological sample measurement sensor 11 are electrically connected via this connector unit.
- Acceleration sensor 5 is desirably arranged so as to be adjacent to this connector portion.
- the acceleration sensor 5 is arranged on the substrate 4 in the vicinity of the control element 6; in other words, it is arranged on the substrate 4 in the vicinity of the control element 6 that functions as a measuring part or a control part. Further, the acceleration sensor 5 is disposed in the vicinity of the sensor insertion portion 1.
- a control element 6 called a microcomputer is disposed on the upper surface of the substrate 4. As shown in FIG. 4, the control element 6 includes a measurement unit 7 to which the sensor insertion unit 1 is connected, a control unit 8 to which the measurement unit 7 is connected, and a determination unit 9 to which the acceleration sensor 5 is connected.
- the memory unit 10 is connected to the determination unit 9. The determination unit 9 and the memory unit 10 are connected to the control unit 8.
- the sensor insertion unit 1 is provided with an insertion detection unit 12 that detects the insertion of the biological sample measurement sensor 11, and the insertion detection unit 12 is connected to the control unit 8. Furthermore, the display unit 3, a buzzer 13 as an example of an alarm unit, and operation buttons 14 and 15 are connected to the control unit 8.
- a biological sample measurement sensor 11 blood glucose level sensor
- the power is turned on (step S1 in FIG. 5).
- blood exuded from the punctured finger is spotted on the spotting part 11a of the biological sample measuring sensor 11 in the state of FIG. 1 (step S5 in FIG. 5).
- the spotted blood reaches a reagent (not shown) in the biological sample measurement sensor 11 from the spotting part 11a, and an electrochemical reaction is caused by the blood and this reagent.
- the signal of the chemical reaction is measured by the measurement unit 7 (S10 in FIG. 5), and the measurement result is displayed on the display unit 3 (S12 in FIG. 5).
- the determination unit 9 determines whether or not the output value is equal to or greater than a predetermined value set in advance (steps S3 and / or S8).
- a flag “excessive impact exists” is recorded in the memory unit 10 in step S4 or step S9.
- control unit 8 determines whether or not the flag is input to the memory unit 10 in step S11. When this flag is present, an error display is displayed on the display unit 3. An error warning may be given with the buzzer 13 together with the display.
- FIGS. 6A to 6D show examples of error display displayed on the display unit 3.
- FIG. 6A shows an error display indicating that an impact has been received in a dot matrix
- FIG. 6B shows an error indicating that an impact has been received using an error code (in the case of a segment display). It is a display.
- FIG. 6C and FIG. 6D will be described in Embodiment 3.
- an excessive impact applied to the sensor insertion portion 1 is detected by the acceleration sensor 5.
- an error is displayed on the display unit 3. This suppresses the display of inappropriate measurement values.
- measurement accuracy is increased.
- the acceleration sensor 5 in order to detect an excessive impact applied to the sensor insertion portion 1 by the acceleration sensor 5, the acceleration sensor 5 is disposed in the sensor insertion portion 1 as shown in FIG. Specifically, the acceleration sensor 5 is mounted on the substrate 4 in the sensor insertion portion 1.
- the acceleration sensor 5 is preferably a three-dimensional type acceleration sensor.
- the three-dimensional type acceleration sensor can measure acceleration components in the X, Y, and Z axis directions. Therefore, according to the three-dimensional type acceleration sensor, the direction of impact and the impact force can be recorded, and the impact received by the sensor insertion portion 1 can be grasped in more detail.
- three-dimensional acceleration sensors also called three-axis acceleration sensors
- a piezoresistive type such as a piezoresistive type, a capacitance type, and a heat detection type.
- the three-dimensional acceleration sensor is also applied to mobile phones, game controllers, hard disk vibration detection, robot posture control, and the like.
- a piezoresistive three-dimensional acceleration sensor is a silicon semiconductor manufacturing technology that forms a diaphragm with a thin surface in an annular shape; a center weight is supported by this thin metal, making it easier to detect displacement due to acceleration; Diaphragm Is detected by a piezoresistive element; amplified and measured by an electric circuit.
- the capacitance type three-dimensional acceleration sensor detects a slight position change in a minute movable part supported by a beam structure as a change in capacitance; it is amplified and measured by an electric circuit.
- a heat-sensing type three-dimensional acceleration sensor is a device that generates a hot air current in a housing of an acceleration sensor with a heater and detects a change in convection due to acceleration by a thermal resistance or the like.
- the acceleration sensor used here is a capacitance type three-dimensional acceleration sensor, and its measurement range is, for example, ⁇ 2 g to +2 g (g: gravitational acceleration).
- the “durability of the main body case 2” refers to a measurement device that is evaluated in a mechanical strength test (for example, a drop test of the measurement device) of the main body case in quality evaluation or shipping inspection of the measurement device. It refers to durability performance that indicates the quality assurance range of mechanical strength. Specifically, in the mechanical strength test, a component mounted on the substrate in the measurement device when a drop test of the measurement device of the finished product (for example, a test of dropping from a height of 1 m onto the floor) is performed. It is tested whether there is a possibility that the performance as a measuring device may be affected by the fact that the device is detached, the substrate is cracked, or the component itself is destroyed.
- the biological sample measurement device of the present embodiment has the acceleration sensor 5 disposed on the substrate 4 inside the main body case 2.
- the acceleration sensor 5 arranged in this way can mainly detect an impact received by the entire body case 2.
- the case where the entire body case 2 is impacted is assumed to be, for example, a case where the body case 2 is dropped during measurement or a case where the body case 2 is inadvertently hit against a surrounding object.
- the biological sample measuring apparatus of this embodiment is equipped with two acceleration sensors 5a and 5b.
- One acceleration sensor 5a is provided at a position corresponding to the sensor insertion portion 1 of the substrate 4 as in the case of the first embodiment; the other acceleration sensor 5b is the same as in the case of the second embodiment. Further, it is provided on the substrate 4 inside the main body case 2.
- the detection result of each acceleration sensor can be mutually utilized to detect the type of impact in detail. Thereby, the reliability of measurement can be further increased.
- the acceleration sensor 5a flips the biological sample measurement sensor 11 with a finger or the like when spotting blood on the spotting portion 11a of the biological sample measurement sensor 11 attached to the sensor insertion unit 1. It is possible to detect the impact of the case. Further, the acceleration sensor 5a can detect when the entire body case 2 receives an impact. On the other hand, since the acceleration sensor 5b is arranged near the center inside the main body case 2, it can detect an impact applied to the entire main body case 2, but detects a small impact such as an impact caused by flipping the biological sample measurement sensor 11. Not enough to
- the biological sample measurement device of this embodiment is equipped with two acceleration sensors as in the third embodiment; however, as shown in FIGS. 9 and 10, the sensor insertion portion 1 can be attached to and detached from the main body case 2. It is configured. That is, the biological sample measurement of the present embodiment includes the main body case 2 provided with the acceleration sensor 5b and the mounting part 16, and the sensor insertion part 1 provided with the acceleration sensor 5a and the insertion detection part 12. The sensor insertion portion 1 is configured to be detachably attachable to the attachment portion 16.
- the mounting portion 16 is provided with a connector portion 16a having a plurality of contact terminals.
- the signals from the acceleration sensor 5a and the insertion detection portion 12 constituting the sensor insertion portion 1 are passed through the connector portion 16a to the main body case. 2 is transmitted to the determination unit 9 and the control unit 8 included in the control element 6 on the substrate 4 in the frame 2.
- a signal of the biological sample measurement sensor 11 inserted into the sensor insertion unit 1 is transmitted to the measurement unit 7 disposed in the control element 6 via the connector unit 16a. Then, a biological sample (for example, blood) is measured (for example, blood glucose level measurement).
- a biological sample for example, blood
- the mounting portion 16 of the main body case 2 may be integrated with the substrate 4. That is, the mounting portion 16 is configured by providing a plurality of contact terminals constituting the connector portion 16 a on the substrate 4 on which the control element 6 is mounted.
- Other sensors for example, a temperature sensor, a humidity sensor, etc. may be provided in the replaceable sensor insertion portion 1 together with the acceleration element sensor 5a.
- FIG. 10 shows a control block diagram of the biological sample measuring apparatus of the present embodiment.
- the control block shown in FIG. 10 is different from the control block of the first and second embodiments (FIG. 4), and includes two acceleration sensors 5a and 5b.
- the two acceleration sensors 5a and 5b are
- the control element 6 is connected to the determination unit 9.
- the signal from the acceleration sensor 5a is transmitted to the determination unit 9 via the connector unit 16a. That is, acceleration information (output information) of the acceleration sensors 5 a and 5 b is input to the determination unit 9.
- the sensor insertion part 1 can be exchanged, so that it can be exchanged when the sensor insertion part 1 and its surroundings are dirty (for example, when blood adheres). Therefore, it is easy to clean and has advantages of excellent maintenance and ease of maintenance, the biological sample measuring device can be maintained in a sanitary manner, and finally contributes to improvement in reliability such as stable operation of the biological sample measuring device.
- the biological sample measurement device of the present embodiment includes an acceleration sensor 5 a on the sensor insertion portion 1 and an acceleration sensor 5 b on the substrate 4.
- FIG. 11 shows an internal cross-sectional view of the vicinity of the sensor insertion part 1 of the biological sample measurement device of the present embodiment; the biological sample measurement sensor 11 is inserted into the sensor insertion part 1.
- a connection terminal (not shown) of the biological sample measurement sensor 11 is in contact with and electrically connected to the contact portion 21 of the contact pin 20.
- main electric circuit parts such as a control unit are omitted for convenience.
- the acceleration sensor 5a is arranged in contact with the contact pin 20. Further, the acceleration sensor 5 a is electrically connected to the substrate 4 via the wiring 29.
- the tip (connection terminal) of the biological sample measurement sensor 11 inserted into the sensor insertion portion 1 is locked to the protrusion 22. That is, the protrusion 22 functions as a stopper of the biological sample measurement sensor 11.
- FIG. 11 shows a state in which the biological sample measurement sensor 11 is locked to the protrusion 22, that is, a state in which the biological sample measurement sensor 11 is correctly set in the sensor insertion portion 1.
- the 8 has an acceleration sensor 5a that is a part of the sensor insertion unit 1 and is provided on the substrate 4.
- the biological sample measurement device of FIG. A part of the acceleration sensor 5a is attached so as to be in contact with the contact pin 20.
- the contact pin 20 bends in the arrow X direction.
- the acceleration sensor 5 a attached in contact with the contact pin 20 detects the vibration of the contact pin 20. In this way, insertion of the biological sample measurement sensor 11 can be detected by the acceleration sensor 5a. Similarly, discharge from the sensor insertion portion 1 of the biological sample measurement sensor 11 can also be detected by the acceleration sensor 5a.
- the biological sample measuring sensor 11 when the blood exuded from the finger is spotted on the spotting portion 11a of the biological sample measuring sensor 11, the biological sample measuring sensor 11 that has been "bent" by the finger
- the acceleration sensor 5a can reliably detect an impact when the deflection is eliminated vigorously, an impact caused by a finger touching the biological sample measurement sensor during measurement, and the like.
- the impact is detected, there is a high possibility that the measured value is not reliable, so that the measured value is not displayed and a warning can be displayed as a measurement failure.
- the reagent in the biological sample measurement sensor 11 moves from a predetermined position, and the measurement value (blood glucose level) becomes erroneously too small or too large. If the reading is too low or too high, the wrong amount of insulin can be administered, causing an accident. In particular, when the measured value becomes too small, insulin is administered more than necessary based on the undermeasured value, and an accident that falls into a very dangerous state of hypoglycemia occurs.
- the blood test apparatus of the present invention can reliably prevent such problems.
- the used biological sample measurement sensor 11 is picked up by hand and discarded.
- the acceleration sensor 5a can also detect an impact caused by these discharging operations.
- the acceleration sensor 5a can also detect both insertion and discharge of the biological sample measurement sensor 11.
- the sensitivity of the acceleration sensor 5a provided in the sensor insertion portion 1 in FIG. 11 and the sensitivity of the acceleration sensor 5b on the substrate 4 may be in different measurement ranges.
- the sensitivity of the acceleration sensor 5a is about 2 to 10 times higher than that of the acceleration sensor 5b.
- an acceleration sensor with a measurement range of ⁇ 2 g to +2 g may be used as the acceleration sensor 5 a
- an acceleration sensor with a measurement range of ⁇ 6 g to +6 g may be used as the acceleration sensor 5 b.
- the threshold value L1 is a threshold value for detecting insertion or ejection of the biological sample measurement sensor 11, and may be set in a range of about 0.01 g to 0.3 g, for example.
- the threshold value L2 is a threshold value for detecting contact with a biological sample measurement sensor such as a finger being measured (detecting that there is a possibility that the measurement value is not reliable). For example, 0.005 g It may be in the range of about ⁇ 0.3 g.
- the threshold value L3 is a threshold value for determining that the measurement itself cannot be performed, and is preferably 0.5 g or more, for example.
- L1 ⁇ L3 L1 ⁇ L3
- L2 ⁇ L3 L1 ⁇ L2 or L1> L2
- the threshold values L1 to L3 may be compared with acceleration data measured by both the acceleration sensor 5a and the acceleration sensor 5b; for that purpose, the threshold values L1 and L2 are mainly set in the sensor insertion unit 1. It is effective to compare with the acceleration data measured by the provided acceleration sensor 5a, and it is more effective to compare the threshold value L3 with the acceleration data measured by the acceleration sensor 5b provided on the substrate 4. For this reason, as described above, the acceleration sensor 5a and the acceleration sensor 5b may select acceleration sensors having different sensitivities.
- the acceleration sensor 5a attached to the sensor insertion portion 1 (on the contact pin 20 in FIG. 11) and the acceleration sensor 5b arranged on the substrate 4 inside the apparatus are preferably three-dimensional acceleration sensors.
- FIG. 12a shows the relationship between each axis (X axis, Y axis, Z axis) of the three-dimensional acceleration sensor and the biological sample measurement sensor.
- the X-axis is parallel to the longitudinal direction of the plate-shaped biological sample measurement sensor 11;
- the Y-axis is orthogonal to the X-axis;
- the Z-axis is orthogonal to each of the X-axis and the Y-axis. That is, perpendicular to the XY plane.
- This relationship is an example, and there is no problem if the reference axis is set to be the same in all of the plurality of acceleration sensors. That is, in FIG.
- a direction parallel to the longitudinal direction of the biological sample measurement sensor is defined as the X axis, and this X axis is used as a reference; a direction parallel to the longitudinal direction of the biological sample measurement sensor is defined as the Y axis.
- the Y axis may be the reference axis, or the direction parallel to the longitudinal direction of the biological sample measurement sensor may be defined as the Z axis, and the Z axis may be the reference axis. That is, there is no problem as long as the X axes, the Y axes, and the Z axes of a plurality of three-dimensional acceleration sensors are set in common (in the same direction).
- the measurement acceleration GA measured by the three-dimensional acceleration sensor 5a shown in FIG. 12a and the measurement acceleration GB measured by the three-dimensional acceleration sensor 5b will be described.
- the accelerations GA and GB are expressed as follows.
- FIG. 12b vector values representing directions and forces are shown.
- GAx represents the x component of GA
- GAy represents the y component of GA
- GAz represents the z component of GA
- GBx represents the x component of GB
- GBy represents the y component of GB
- GBz represents the z component of GB (the same applies hereinafter).
- GA GAx + GAy + GAz (shows the sum of vectors of X, Y, Z axis components)
- GB GBx + GBy + GBz (shows the sum of vectors of X, Y, Z axis components)
- the measurement accelerations GA and GB are defined as follows according to the measurement time. Measurement acceleration measured when the biological sample measurement sensor 11 is inserted into the sensor insertion slot 1: GA1, GB1 Measurement acceleration measured during blood glucose measurement: GA2 and GB2 (measurement acceleration GA2 and GB2 are not necessarily one each, and are usually measured multiple times) Measurement acceleration measured when the biological sample measurement sensor 11 is discharged from the sensor insertion slot 1: GA3, GB3
- the measured acceleration GA2 and GB2 Based on the measured acceleration GA2 and GB2, it can be determined as follows. If the measurement accelerations GA2 and GB2 cannot be measured, it is determined that the biological sample measurement device itself has an error (failure). In the case of “measurement acceleration GA2, GB2> threshold L3”, it is determined that the measurement of the biological sample cannot be performed, and confirmation of whether there is a failure of the measurement apparatus and remeasurement are obtained. In the case of “threshold L3> measurement acceleration GA2, GB2> threshold L2,” it is determined that there is a possibility that appropriate measurement has not been performed, and the biological sample measurement sensor is replaced and remeasured. In the case of “measurement acceleration GA2, GB2 ⁇ threshold L2,” it is determined that appropriate measurement has been performed.
- the measured acceleration GA2 and the threshold value L2 can be compared to determine whether or not appropriate measurement has been performed. Further, when the sensitivities of the acceleration sensors 5a and 5b are different, the measured accelerations GA2 and GB2 obtained by converting the sensitivity of the data input from the acceleration sensors 5a and 5b are compared with the thresholds L2 and L3, respectively. . Sensitivity conversion is performed by the determination unit 9 or the control unit 8 (see FIG. 10 and the like).
- the following determination can also be made.
- the blood sugar level cannot be measured due to an impact during blood sugar level measurement.
- threshold value L2 it is determined that there is a possibility that an appropriate blood glucose level measurement has not been performed due to an impact during measurement. If “measurement acceleration components GA2x, GA2y, GA2z, GB2x, GB2y, and GB2z ⁇ threshold L2”, it is determined that appropriate measurement has been performed.
- FIG. 12c illustrates an output signal waveform Wg in the Z-axis direction, which is one of signals output from the three-dimensional acceleration sensor 5a when a finger or the like touches the biological sample measurement sensor 11 during measurement of a blood sugar level or the like.
- Wg an output signal waveform
- FIG. 12c illustrates an output signal waveform Wg in the Z-axis direction, which is one of signals output from the three-dimensional acceleration sensor 5a when a finger or the like touches the biological sample measurement sensor 11 during measurement of a blood sugar level or the like.
- An example is shown.
- the case where it changes notably in the direction perpendicular to the plane of the biological sample measurement sensor 11, that is, in the Z-axis direction, from the arrangement relationship of the sensor insertion portion and the contact pin is considered.
- the data of the output signal Wg which is a change in the measured acceleration value in the Z-axis direction, is taken into the determination unit 9 from the three-dimensional acceleration sensor 5a and stored in the memory unit 10.
- the measurement acceleration data of these acceleration sensors 5a and the threshold value L2 are compared, and the determination unit 9 determines whether or not the threshold value L2 is exceeded.
- the initial peak values of the Z-axis output signal Wg P1, P3, P5, etc., which are positive side peak values, and P2, P4, P6, etc., which are negative side peak values
- P1, P3, P5, etc. which are positive side peak values
- P2, P4, P6, etc. which are negative side peak values
- the output signal Wg has positive peak values P1 and P3 exceeding the threshold value + L2 and is a vibration waveform.
- the output signal Wg has negative peak values P2 and P4 that are lower than the threshold ⁇ L2, and is an oscillation waveform.
- the vibration waveform as shown in FIG. that is, the waveform is not a waveform in which the peak value gradually attenuates with respect to time as shown in FIG. 12c, but after a large peak value is produced at the time of impact as shown in FIG. In many cases, the waveform looks like this.
- FIG. 12d shows an example of the output signal Wg of the Z-axis component of the three-dimensional acceleration sensor 5a when the measuring device falls or the measuring device collides with something outside.
- the peak P1 at the time of impact is not only the threshold value + L2, but also a high peak exceeding the positive side threshold value L3 (+ L3: L3 is the “threshold value for determining that the measurement itself cannot be performed”).
- the value is shown. That is, by comparing the peak value P1 of the measured acceleration data of the Z-axis component of the measured acceleration GA of the capacitive three-dimensional acceleration sensor 5a (corresponding to GA2 when measuring) and the threshold L3 (+ L3). Determine the error. That is, it is possible to make a determination based on the magnitude of the impact.
- FIG. 12d is an example in which the peak values of both P1 and P2 are larger than the threshold value L3; this is not the only case, but only the peak P1 may be larger than the threshold value L3, or only the peak P2 is It may be larger than the threshold value L3. This is because the strength of the impact and the direction of the impact occur differently and are not limited. Therefore, it is necessary to compare the peak values on both the + side and the ⁇ side with threshold values (+ L3, ⁇ L3, etc.).
- the present invention by monitoring the output signal Wg from the acceleration sensor, not only the magnitude of the impact but also the waveform of the output signal Wg is confirmed (whether it is a vibration waveform or the like). Thus, the cause of the impact can be determined. Thereby, the user can be instructed / displayed / notified with accurate caution / warning in biological sample measurement, and can improve the stable use and reliability of the measuring apparatus.
- FIG. 12c shows an example of a vibration waveform that gradually attenuates, but the shape of the waveform is not limited to this.
- the vibration waveform as shown in FIG. 12c may have various waveform shapes because elements such as the peak value, the frequency or period of vibration, and the decay time may be different. Furthermore, not a vibration waveform but a transient waveform may be observed when the measuring device falls. Thus, there are various forms of external impact on the measuring apparatus, and various waveform patterns can be considered.
- the measured acceleration component may be compared with the threshold value L2 or L3.
- FIG. 13 shows an example of a waveform pattern of an applied voltage for performing blood glucose level measurement.
- the measurement timing of the acceleration sensor will be described.
- FIG. 13 shows a waveform of an applied voltage supplied from a measurement device to a detection electrode (electrode for measurement such as a working electrode or a counter electrode) of a biological sample measurement sensor in order to measure a blood glucose level (glucose level).
- FIG. 13 shows a case where three multi-pulse waveforms (rectangular waves) are applied.
- an applied voltage V1 (eg, 350 mV; possible in the range of 100 to 800 mV) is applied for t1 time (eg; 2 seconds; about 0.5 to 5 seconds) from the start of measurement.
- the subsequent t4 time eg, 1 second; about 0.1 to 3 seconds
- no voltage is applied.
- the applied voltage V2 (eg, 250 mV; possible in the range of 100 to 800 mV) is applied again for t2 time (eg; 2 seconds; 0.5 to 5 seconds).
- the voltage is not applied for the subsequent t5 time (example: 0.1 second; 0 to 1.0 second).
- an applied voltage V3 (example: 2.5 v; 1.5 to 3.5 V) is applied for t3 time (example: 0.5 seconds; 0.1 to 2 seconds).
- the pulse PW1 and the pulse PW2 indicate voltage application for measuring glucose or voltage application for measuring an interfering substance (a substance that affects glucose value measurement).
- a pulse PW3 indicates voltage application for measuring an Hct (hematocrit) value.
- FIG. 14 shows an output signal from the detection electrode (working electrode, counter electrode, etc.) of the biological sample measurement sensor when, for example, blood glucose level measurement is applied when the pulse application voltage shown in FIG. 13 is applied.
- W1 represents an output signal from the detection electrode (working electrode, counter electrode, etc.) when the pulse voltage PW1 (application voltage V1, application time t1) is applied.
- W2 represents an output signal when the pulse voltage PW2 (applied voltage V2, applied time t2) is applied. It is an output signal corresponding to a reaction current due to an oxidation-reduction reaction in a biological sample measurement sensor, that is, a glucose value.
- W3 represents an output signal from the Hct electrode when the pulse voltage PW3 (applied voltage V3, applied time t3) is applied.
- the glucose value blood glucose level at the reference temperature is obtained.
- the reagent in the reaction dissolved with blood deviates from a predetermined position (for example, on the detection electrode) and is appropriately As a result, the glucose level is not accurate or the measurement itself is not possible.
- a shock is applied to the measurement device, the measurement device is shocked from the outside, the measurement device is dropped, a finger touches the biological sample measurement sensor, or blood is spotted on the biological sample measurement sensor. A case where the biological sample measurement sensor is pressed strongly to bend is sometimes considered.
- This problem can be solved by using a measuring device equipped with an acceleration sensor. That is, whether or not an impact has occurred during measurement is accurately detected, and if an impact is detected during measurement, it is determined that the measurement data is not accurate. Therefore, measurement data is not displayed, an error is displayed, and re-measurement is prompted. As a result, only reliable measurement values are displayed on the display unit, and the reliability of the measurement apparatus is improved.
- the output signal W1, W2 or W3 in FIG. 15 often has an abnormal waveform. Therefore, it is possible to detect that an impact has been received from the waveform of the output signal W1, W2 or W3.
- no output signal is output in the time zone in which no voltage is applied (time zone t4 and t5 in FIG. 13) or immediately before the start of measurement (before voltage application)
- an impact is detected from the output signal waveform. It ’s difficult. Therefore, detection by an acceleration sensor is important.
- FIGS. 13 and 14 show the case where the applied voltage waveform is a multi-waveform including three waveforms PW1, PW2, and PW3.
- the multi-waveform including two waveforms (when not applied for Hct value measurement) is shown.
- the same effect can be obtained even when it is a multi-waveform including four or more waveforms (three or more glucose measurement applications).
- impacts at all timings of blood glucose level measurement can be reliably detected. Thereby, only the highly reliable measurement value is displayed on the display unit, so far, the measurement value becomes insufficient due to an external impact, and an extra dose of insulin is administered based on the undermeasurement value; Therefore, it is possible to prevent the occurrence of an accident that causes a dangerous hypoglycemia state. As a result, the reliability and safety of the measuring apparatus are further ensured.
- FIG. 15 shows a modification of the biological sample measurement device such as the blood glucose level measurement of FIGS. 9 and 10, and includes a measurement device main body 40 having a display unit 47 and a cover 41 covering a part of the measurement device main body 40.
- the biological sample measuring device containing these.
- the cover 41 is provided with a sensor insertion portion 1 for inserting the biological sample measurement sensor 11, and an acceleration sensor 5 a is provided on the back surface of the cover 41.
- the acceleration sensor 5a provided on the back surface of the cover 41 is connected to the measuring device via the wiring 42, the connecting portion 43, and the connecting portion 44 of the measuring device body when the cover 41 is attached to the measuring device body 40. It is electrically connected to an electric circuit such as a control unit mounted inside the main body 40. As a result, when the cover 41 is attached to the apparatus main body 40, power is supplied from the apparatus main body 40 to the acceleration sensor 5a via the connection portion 44 and the signal from the acceleration sensor 5a is also transmitted to the apparatus main body 40 side. Can be sent to.
- connection electrode portion 11 b of the biological sample measurement sensor 11 connected to a working electrode or a counter electrode that is a detection electrode for measurement
- sensor contact portion 46 of the measurement apparatus main body 40 By contacting 45, the biological sample measurement sensor 11 is electrically connected to an electrical circuit such as a measurement unit in the measurement apparatus main body 40.
- the replaceable cover 41 by providing the replaceable cover 41 with the acceleration sensor 5a, it is possible to use acceleration sensors having different sensitivities by replacing the cover 41.
- Another acceleration sensor 5b (not shown) may be provided on the substrate 4 of the measurement apparatus main body 40.
- By changing the sensitivity of the two acceleration sensors 5a and 5b it is possible to detect impacts of different magnitudes. Thereby, the impact touching the biological sample measurement sensor 11 is detected with high sensitivity, the detection performance at the time of measurement is improved, and a more reliable measurement and a highly reliable measurement device can be realized. .
- FIG. 16 shows an operation flow in which the acceleration sensor 5a or the like detects whether or not “addition”, which is the additional spotting, has been made.
- the acceleration is detected by the acceleration sensor 5 a (see FIG. 11 or the like) arranged in the sensor insertion unit 1.
- the steps S21 to S33 will be specifically described below.
- S21 Check that the biological sample measurement sensor 11 is mounted. Whether or not the biological sample measurement sensor 11 is attached to the sensor insertion portion 1 (see FIG. 11 and the like) is determined based on the contact portion 16a on the measurement device side (see FIG. 12 and the like) that contacts the connection electrode portion 11b (see FIG. 12 and the like) of the biological sample measurement sensor 11. This is confirmed by confirming the continuity / resistance value between the terminals of the plurality of contact pins 20 (see FIGS. 9 and 15). If the wearing of the biological sample measurement sensor 11 can be confirmed, the process proceeds to step S22.
- S23 The type of the mounted biological sample measurement sensor 11 is determined.
- the model discrimination is performed based on the difference in pattern provided on the connection electrode portion 11b of the biological sample measurement sensor 11.
- step S24 If the determined model is not appropriate, the process proceeds to step S25; if the determined model is appropriate, the process proceeds to step S26.
- S25 A model error ("E7" error code in the figure) is displayed, and an instruction is given to replace the biological sample measurement sensor 11 with a regular one. Then, the process proceeds to S21.
- S26 Display prompting “blood spotting” to prompt the user to spot the biological sample measurement sensor 11.
- S27 It is determined whether or not blood is spotted on the spotting portion 11a of the biological sample measurement sensor 11. Confirmation of blood spotting is performed by providing a plurality of “detection electrodes” in the inflow direction of blood, and detecting changes in resistance values between the electrodes of the detection electrodes due to the inflow of blood. For example, at the first detection electrode closest to the spotting part 11a of the biological sample measurement sensor 11, the spotting of blood is first detected. When the spotting of blood is confirmed, the process proceeds to step S28.
- Blood spotting can also be indirectly detected by the acceleration sensor 5a (see FIG. 11 and the like). That is, when the blood exuded on the user's finger is spotted on the spotting portion 11 a at the tip of the biological sample measurement sensor 11, the finger naturally contacts the biological sample measurement sensor 11. The contact can be detected by the acceleration sensor 5a. In this case, it is only necessary to detect that the finger and the biological sample measurement sensor 11 are in contact with each other.
- the threshold value L4 for detecting the contact between the finger and the biological sample measurement sensor is preferably set to a value smaller than the threshold value L2 for determining the impact during measurement.
- the threshold L4 may be about 0.005 to 0.3 g, for example.
- step S28 Whether or not blood has sufficiently flowed into the capillary (supply path; not shown) of the sensor 11a is detected by the second detection electrode (the detection electrode at the position farthest from the spotting portion 11a). If the inflow of blood is detected, it is determined that a sufficient amount of blood necessary for measurement has flowed into the capillary (supply channel) of the biological sample measurement sensor 11, and the process proceeds to step S33. On the other hand, if it is determined that the inflow of blood is insufficient, the process proceeds to step S29.
- the second detection electrode is preferably disposed at a position farthest from the spotting portion 11a, but the back side of the capillary (the spotting portion) rather than the detection electrode such as a working electrode or a counter electrode for detecting the oxidation-reduction reaction current. It suffices to be disposed on the side farther than 11a.
- a waiting time (follow-up waiting time) until “follow-up (addition spotting)” is set is set.
- the additional waiting time is, for example, about 10 seconds to 120 seconds, and preferably 15 to 60 seconds.
- S30 The additional waiting time is monitored, and if the waiting time is exceeded, it is determined that the error is due to “poor spotting” / “poor amount of spotting”.
- the display unit 3 is then alerted by an error display and a sounder to prompt the user to replace the biological sample measurement sensor 11 and perform the measurement again.
- the acceleration sensor 5a detects whether or not the user's finger has touched the spotting portion 11a, and determines whether or not the biological sample measurement sensor 11 has been spotted additionally. Basically, it is the same as step S27, and the same applies to the setting of the threshold value L4. If it is detected that the additional spotting has been performed, the process proceeds to step S32. When it cannot detect, it returns to step S30.
- step S32 Similarly to step S28, the inflow of blood is detected from a change in the resistance value between the second detection electrode located farthest from the spotting portion 11a (the farthest) and the predetermined electrode. If blood is detected, it is determined that sufficient blood for measurement has flowed into the capillary (supply channel) of the biological sample measurement sensor 11, and the process proceeds to step S33. If it is determined that the blood is insufficient, the process returns to step S30.
- the present invention includes a main body case having a sensor insertion part, a measurement part connected to the sensor insertion part, a control part connected to the measurement part, and a display part connected to the control part, Since the acceleration sensor for detecting the impact applied to the sensor insertion portion is provided, the reliability of the measurement value can be improved and the measurement accuracy can be improved.
- the acceleration sensor detects an impact on the sensor insertion portion via the biological sample measurement sensor. If the impact detected by the acceleration sensor exceeds the specified value, the measurement result measured by the measurement unit is considered inappropriate, the measurement value is not displayed, and the measurement is inappropriate on the display unit. Can be displayed. Therefore, it is possible to prevent an inappropriate measurement result having a problem in reliability from being displayed and to improve measurement accuracy. Therefore, it is expected to be used as a biological sample measuring device for measuring blood sugar levels, lactic acid levels, and the like.
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Physics & Mathematics (AREA)
- Biomedical Technology (AREA)
- Molecular Biology (AREA)
- Pathology (AREA)
- General Health & Medical Sciences (AREA)
- Biophysics (AREA)
- Public Health (AREA)
- Medical Informatics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Veterinary Medicine (AREA)
- Chemical & Material Sciences (AREA)
- Optics & Photonics (AREA)
- Analytical Chemistry (AREA)
- Biochemistry (AREA)
- General Physics & Mathematics (AREA)
- Immunology (AREA)
- Emergency Medicine (AREA)
- Urology & Nephrology (AREA)
- Food Science & Technology (AREA)
- Medicinal Chemistry (AREA)
- Chemical Kinetics & Catalysis (AREA)
- Electrochemistry (AREA)
- Investigating Or Analysing Biological Materials (AREA)
Abstract
Description
図1は、本実施形態の生体試料測定装置の斜視図であり;図2は、その断面図であり;図3は、その上面図であり;図4は、その制御ブロック図である。図1に示すように、本実施形態の生体試料測定装置は、その一端にセンサ挿入部1を有する本体ケース2を備える。センサ挿入部1には、点着部11aを有するセンサ11が挿入可能に構成されている。
本実施形態の生体試料測定装置は、図7に示すように、加速度センサ5を本体ケース2の内部の基板4の上に配置している。このように配置された加速度センサ5は、主に、本体ケース2の全体が受けた衝撃を検出することができる。本体ケース2の全体が衝撃を受けるとは、例えば、本体ケース2を測定中に落下させた場合や、本体ケース2を周囲の物体に不注意でぶつけた場合などが想定される。
本実施形態の生体試料測定装置は、図8に示すように、2つの加速度センサ5aと5bを搭載している。一方の加速度センサ5aは、実施の形態1に示す場合と同様に、基板4のセンサ挿入部1に対応した位置に設けており;他方の加速度センサ5bは、実施の形態2に示す場合と同様に、本体ケース2の内部の基板4に設けている。
本実施形態の生体試料測定装置は、実施の形態3と同様に2つの加速度センサを搭載するが;図9と図10に示されるように、センサ挿入部1が、本体ケース2に着脱可能に構成されている。すなわち、本実施形態の生体試料測定は、加速度センサ5bと装着部16とが設けられた本体ケース2と、加速度センサ5aと挿入検知部12とが設けられたセンサ挿入部1とを有し、センサ挿入部1は、着脱可能に装着部16に装着できるように構成されている。
本実施形態の生体試料測定装置は、図11に示すように、加速度センサ5aをセンサ挿入部1に、加速度センサ5bを基板4上に設けている。図11は、本実施形態の生体試料測定装置のセンサ挿入部1付近の内部断面図を示しており;生体試料測定センサ11が、センサ挿入部1に挿入された状態を示す。生体試料測定センサ11の接続端子(不図示)は、コンタクトピン20の接触部21と接触し、電気的に接続されている。なお、図11では、制御部などの主な電気回路部分は、便宜上省略している。
(1) L1 < L3
(2) L2 < L3
(3) L1≦L2 または L1>L2
GA=GAx+GAy+GAz(X,Y,Z軸成分のベクトルの総和を示す)
GB=GBx+GBy+GBz(X,Y,Z軸成分のベクトルの総和を示す)
生体試料測定センサ11をセンサ挿入口1に挿入したときに測定した測定加速度:GA1、GB1
血糖値測定中に測定した測定加速度:GA2、GB2(測定加速度GA2およびGB2は、それぞれ1つとは限らず、通常は複数回測定される)
生体試料測定センサ11をセンサ挿入口1から排出したときに測定した測定加速度:GA3、GB3
図13は、血糖値測定を行うための印加電圧の波形パターンの例を示している。ここで、加速度センサの測定タイミングについて説明する。図13は、血糖値(グルコース値)を測定するために、測定装置から生体試料測定センサの検出電極(作用極や対極など測定のための電極)に供給する印加電圧の波形を示す。図13は、3つのマルチパルス波形(矩形波)を印加する場合を示している。
図15は、図9および図10の血糖値測定などの生体試料測定装置の変形例を示すものであり、表示部47を有する測定装置本体40と、測定装置本体40の一部を覆うカバー41とを含む生体試料測定装置を示す。カバー41には、生体試料測定センサ11を挿入するためのセンサ挿入部1が設けられており、さらにカバー41の裏面には加速度センサ5aが設けられている。
生体試料測定センサ11への生体試料の点着量が少なすぎると、適切な生体成分量の測定(例:血糖値測定など)ができない。その場合に、生体試料を追加点着(「追い足し」ともいう)してから、測定を行うことがある。そのため、生体試料の点着量が少なすぎると判断してから、追加点着を受けるまで、所定の時間待機することが必要になる場合がある。図16は、その追加点着である「追い足し」がなされたかどうかを、加速度センサ5aなどにより検知する動作フローを示す。図16に示される動作フローでは、センサ挿入部1に配置された加速度センサ5a(図11など参照)で追い足しを検知する。以下、各ステップS21~S33について具体的に説明する。
S25:機種エラー(図では、“E7”のエラーコード)を表示し、生体試料測定センサ11を正規のものと交換するように指示する。そして、S21へ移行する。
S26:「血液の点着」を促す表示をして、生体試料測定センサ11の点着をユーザに促す。
2 本体ケース
3 表示部
4 基板
5,5a,5b 加速度センサ
6 制御素子
7 測定部
8 制御部
9 判定部
10 メモリ部
11 生体試料測定センサ
11a 点着部
12 挿入検知部
13 ブザー
14、15 操作ボタン
16 装着部
16a コネクタ部
20 コンタクトピン
21 接触部
22 突起
29 配線
40 測定装置本体
41 カバー
42 配線
43 接続部
44 接続部
45 コンタクトピン
46 センサコンタクト部
47 表示部
Claims (10)
- センサ挿入部を有する本体ケースと、前記センサ挿入部に接続された測定部と、前記測定部に接続された制御部と、前記制御部に接続された表示部と、を備え、
前記センサ挿入部に加わる衝撃を検出する加速度センサを設けた生体試料測定装置。 - 前記加速度センサは、前記センサ挿入部に配置されている、請求項1に記載の生体試料測定装置。
- 前記センサ挿入部は、前記センサ挿入部に挿入される生体試料測定センサと接触するコンタクトピンを有し、
前記加速度センサは、前記コンタクトピンに配置されている、請求項1に記載の生体試料測定装置。 - 前記コンタクトピンは、前記センサ挿入部に挿入される前記生体試料測定センサと接触し、
前記生体試料測定センサが振動すると、前記振動が、前記コンタクトピンを経由して、前記加速度センサに伝達される、請求項3に記載の生体試料測定装置。 - 前記加速度センサに接続され、衝撃が加わった時、前記加速度センサから出力される信号を検出する判定部と、前記判定部に接続されたメモリ部とをさらに有し、
前記判定部および前記メモリ部は、前記制御部に接続されている、請求項1に記載の生体試料測定装置。 - 前記加速度センサは、3次元加速度センサである、請求項1に記載の生体試料測定装置。
- 前記測定部及び前記制御部は、前記本体ケース内の電気回路基板に配置され、
前記加速度センサは、前記センサ挿入部近傍の前記電気回路基板に配置されている、請求項1に記載の生体試料定装置。 - 複数の前記加速度センサを有する、請求項1に記載の生体試料測定装置。
- 複数の前記加速度センサのうち、少なくとも1つは、前記センサ挿入部に配置されている、請求項8に記載の生体試料測定装置。
- 複数の前記加速度センサのうち、少なくとも1つは、3次元加速度センサである、請求項8に記載の生体試料測定装置。
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CN201280006779.7A CN103354901B (zh) | 2011-03-28 | 2012-03-28 | 生物试样测定装置 |
US14/001,954 US8834691B2 (en) | 2011-03-28 | 2012-03-28 | Device for measuring biological sample |
EP12765681.7A EP2693208B1 (en) | 2011-03-28 | 2012-03-28 | Device for measuring biological sample |
EP17188359.8A EP3270147B1 (en) | 2011-03-28 | 2012-03-28 | Device for measuring biological sample |
JP2013507185A JP5798618B2 (ja) | 2011-03-28 | 2012-03-28 | 生体試料測定装置 |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2011-069226 | 2011-03-28 | ||
JP2011069226 | 2011-03-28 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2012132432A1 true WO2012132432A1 (ja) | 2012-10-04 |
Family
ID=46930204
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2012/002155 WO2012132432A1 (ja) | 2011-03-28 | 2012-03-28 | 生体試料測定装置 |
Country Status (5)
Country | Link |
---|---|
US (1) | US8834691B2 (ja) |
EP (2) | EP3270147B1 (ja) |
JP (3) | JP5798618B2 (ja) |
CN (1) | CN103354901B (ja) |
WO (1) | WO2012132432A1 (ja) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2014032178A (ja) * | 2012-07-12 | 2014-02-20 | Panasonic Corp | 液体試料測定装置 |
WO2014099419A1 (en) * | 2012-12-17 | 2014-06-26 | Abbott Point Of Care Inc | A portable clinical analysis system for hematocrit measurement |
JP2015206804A (ja) * | 2011-03-28 | 2015-11-19 | パナソニックヘルスケアホールディングス株式会社 | 生体試料測定装置 |
US9885706B2 (en) | 2012-12-17 | 2018-02-06 | Abbott Point Of Care Inc. | Portable clinical analysis system for immunometric measurement |
US9904761B2 (en) | 2012-12-17 | 2018-02-27 | Abbot Point Of Care Inc. | Self correction for spatial orientation and motion of portable clinical analyzers |
US9915643B2 (en) | 2012-12-17 | 2018-03-13 | Abbott Point Of Care Inc. | Spatial orientation determination in portable clinical analysis systems |
US9952194B2 (en) | 2012-12-17 | 2018-04-24 | Abbott Point Of Care Inc. | Operation and verification of a portable clinical analysis system |
Families Citing this family (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7925449B2 (en) * | 2006-09-18 | 2011-04-12 | Cfph, Llc | Products and processes for analyzing octane content |
US9823214B2 (en) * | 2011-11-01 | 2017-11-21 | Panasonic Healthcare Holdings Co., Ltd. | Biological sample measuring apparatus |
US9623409B2 (en) | 2013-03-11 | 2017-04-18 | Cue Inc. | Cartridges, kits, and methods for enhanced mixing for detection and quantification of analytes |
US10545161B2 (en) | 2013-03-11 | 2020-01-28 | Cue Health Inc. | Systems and methods for detection and quantification of analytes |
IL297030B2 (en) | 2013-03-11 | 2024-03-01 | Cue Health Inc | A method for activating fluid flow within a microfluidic cartridge |
USD745423S1 (en) | 2014-05-12 | 2015-12-15 | Cue Inc. | Automated analyzer test cartridge and sample collection device for analyte detection |
US20150330937A1 (en) * | 2014-05-16 | 2015-11-19 | Lifescan Scotland Limited | Hand-held test meter with body portion proximity sensor module |
USD742524S1 (en) * | 2014-11-17 | 2015-11-03 | Bayer Healthcare Llc | Analyte meter |
BR122020004273B1 (pt) | 2015-07-17 | 2022-11-29 | Cue Health Inc | Cartucho de análise de amostras |
US11237161B2 (en) | 2017-01-25 | 2022-02-01 | Cue Health Inc. | Systems and methods for enhanced detection and quantification of analytes |
US11346805B2 (en) * | 2017-02-07 | 2022-05-31 | Colorado State University Research Foundation | Handheld electrochemical sensing platform |
US11408881B2 (en) | 2017-05-04 | 2022-08-09 | Roche Diabetes Care, Inc. | Test meter and method for detecting undue pressure applied to an inserated test strip |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2010052849A1 (ja) * | 2008-11-04 | 2010-05-14 | パナソニック株式会社 | 測定装置、インスリン注入装置、測定方法、インスリン注入装置の制御方法及びプログラム |
JP2010266217A (ja) * | 2009-05-12 | 2010-11-25 | Panasonic Corp | 携帯型血糖値測定装置 |
Family Cites Families (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2000283789A (ja) | 1999-03-30 | 2000-10-13 | Yamasa Tokei Keiki Kk | 歩数計 |
US20060091006A1 (en) * | 1999-11-04 | 2006-05-04 | Yi Wang | Analyte sensor with insertion monitor, and methods |
CN100346158C (zh) | 2000-11-30 | 2007-10-31 | 松下电器产业株式会社 | 基质的定量方法 |
DE60324738D1 (de) * | 2002-07-18 | 2009-01-02 | Panasonic Corp | Messvorrichtung mit einem Biosensor |
US7132041B2 (en) * | 2003-02-11 | 2006-11-07 | Bayer Healthcare Llc | Methods of determining the concentration of an analyte in a fluid test sample |
WO2007131036A1 (en) * | 2006-05-03 | 2007-11-15 | Bayer Healthcare Llc | Underfill detection system for an electrochemical biosensor |
US20080125700A1 (en) * | 2006-11-29 | 2008-05-29 | Moberg Sheldon B | Methods and apparatuses for detecting medical device acceleration, temperature, and humidity conditions |
JP4825762B2 (ja) * | 2006-12-20 | 2011-11-30 | 株式会社タニタ | 被験液測定装置及び感度較正方法 |
JP5345522B2 (ja) * | 2007-03-30 | 2013-11-20 | テルモ株式会社 | 体液成分測定装置 |
JP2010063576A (ja) * | 2008-09-10 | 2010-03-25 | Panasonic Corp | 血液検査装置 |
CN103354901B (zh) * | 2011-03-28 | 2015-09-09 | 松下健康医疗控股株式会社 | 生物试样测定装置 |
-
2012
- 2012-03-28 CN CN201280006779.7A patent/CN103354901B/zh active Active
- 2012-03-28 US US14/001,954 patent/US8834691B2/en active Active
- 2012-03-28 EP EP17188359.8A patent/EP3270147B1/en active Active
- 2012-03-28 WO PCT/JP2012/002155 patent/WO2012132432A1/ja active Application Filing
- 2012-03-28 JP JP2013507185A patent/JP5798618B2/ja active Active
- 2012-03-28 EP EP12765681.7A patent/EP2693208B1/en active Active
-
2015
- 2015-08-20 JP JP2015162793A patent/JP6000418B2/ja active Active
-
2016
- 2016-08-29 JP JP2016167037A patent/JP6209657B2/ja active Active
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2010052849A1 (ja) * | 2008-11-04 | 2010-05-14 | パナソニック株式会社 | 測定装置、インスリン注入装置、測定方法、インスリン注入装置の制御方法及びプログラム |
JP2010266217A (ja) * | 2009-05-12 | 2010-11-25 | Panasonic Corp | 携帯型血糖値測定装置 |
Non-Patent Citations (1)
Title |
---|
See also references of EP2693208A4 * |
Cited By (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2015206804A (ja) * | 2011-03-28 | 2015-11-19 | パナソニックヘルスケアホールディングス株式会社 | 生体試料測定装置 |
JP2017223714A (ja) * | 2012-07-12 | 2017-12-21 | パナソニックヘルスケアホールディングス株式会社 | 液体試料測定装置 |
JP2014032178A (ja) * | 2012-07-12 | 2014-02-20 | Panasonic Corp | 液体試料測定装置 |
US9039875B2 (en) | 2012-07-12 | 2015-05-26 | Panasonic Healthcare Holdings Co., Ltd. | Liquid sample measuring device |
US9904761B2 (en) | 2012-12-17 | 2018-02-27 | Abbot Point Of Care Inc. | Self correction for spatial orientation and motion of portable clinical analyzers |
US9885706B2 (en) | 2012-12-17 | 2018-02-06 | Abbott Point Of Care Inc. | Portable clinical analysis system for immunometric measurement |
WO2014099419A1 (en) * | 2012-12-17 | 2014-06-26 | Abbott Point Of Care Inc | A portable clinical analysis system for hematocrit measurement |
US9915643B2 (en) | 2012-12-17 | 2018-03-13 | Abbott Point Of Care Inc. | Spatial orientation determination in portable clinical analysis systems |
US9949674B2 (en) | 2012-12-17 | 2018-04-24 | Abbott Point Of Care Inc. | Portable clinical analysis system for hematocrit measurement |
US9952194B2 (en) | 2012-12-17 | 2018-04-24 | Abbott Point Of Care Inc. | Operation and verification of a portable clinical analysis system |
US10188327B2 (en) | 2012-12-17 | 2019-01-29 | Abbott Point Of Care Inc. | Portable clinical analysis system for hematocrit measurement |
US10468123B2 (en) | 2012-12-17 | 2019-11-05 | Abbott Point Of Care Inc. | Self correction for spatial orientation and motion of portable clinical analyzers |
US10877019B2 (en) | 2012-12-17 | 2020-12-29 | Abbott Point Of Care, Inc. | Operation and verification of a portable clinical analysis system |
US10942173B2 (en) | 2012-12-17 | 2021-03-09 | Abbott Point Of Care Inc. | Portable clinical analysis system for immunometric measurement |
Also Published As
Publication number | Publication date |
---|---|
JP2015206804A (ja) | 2015-11-19 |
EP3270147B1 (en) | 2023-08-02 |
CN103354901B (zh) | 2015-09-09 |
EP2693208B1 (en) | 2017-10-11 |
CN103354901A (zh) | 2013-10-16 |
EP2693208A4 (en) | 2014-08-13 |
JP6000418B2 (ja) | 2016-09-28 |
EP2693208A1 (en) | 2014-02-05 |
JPWO2012132432A1 (ja) | 2014-07-24 |
US8834691B2 (en) | 2014-09-16 |
JP5798618B2 (ja) | 2015-10-21 |
EP3270147A1 (en) | 2018-01-17 |
JP2017021038A (ja) | 2017-01-26 |
JP6209657B2 (ja) | 2017-10-04 |
US20130334041A1 (en) | 2013-12-19 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
JP6209657B2 (ja) | 生体試料測定装置 | |
CN101952700B (zh) | 电子体温计 | |
JP5738838B2 (ja) | 分析装置、分析方法及び分析システム | |
CN105407800A (zh) | 脑功能障碍评价方法、脑功能障碍评价装置及其程序 | |
KR20140130039A (ko) | 분석물 측정기의 검사 스트립 감지 | |
EP3075310A1 (en) | Method and apparatus for measuring bio signal | |
EP2616802B1 (en) | Method and apparatus for encoding test strips | |
WO2010121080A1 (en) | Method and device for detecting usb cable connection | |
JP5212990B2 (ja) | 分析装置 | |
JP6484315B2 (ja) | 液体試料測定装置 | |
JP2006015068A (ja) | 生体情報測定センサおよび生体情報測定装置 | |
US10514280B2 (en) | Triggering a process in a measuring unit using a movement pattern | |
JP2009229130A (ja) | 電子体温計 | |
KR101900893B1 (ko) | 카트리지형 생체 정보 측정 장치 | |
CN111603156B (zh) | 提高心电图有效测量的方法及其心电测量装置 | |
JP2014165896A (ja) | 携帯端末 | |
EP3418737B1 (en) | Test meter and method for detecting undue pressure applied to an inserted test strip | |
JP2018132411A (ja) | 成分測定装置、及び成分測定装置の点検実施方法 | |
JP2012177677A (ja) | 分析装置 | |
JP3117358U (ja) | 識別機能を有する生物計測器試験片及びその計測器 | |
JP2009198379A (ja) | 電子体温計 | |
TW200829899A (en) | Detecting apparatus and detecting board thereof |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 12765681 Country of ref document: EP Kind code of ref document: A1 |
|
ENP | Entry into the national phase |
Ref document number: 2013507185 Country of ref document: JP Kind code of ref document: A |
|
REEP | Request for entry into the european phase |
Ref document number: 2012765681 Country of ref document: EP |
|
WWE | Wipo information: entry into national phase |
Ref document number: 14001954 Country of ref document: US Ref document number: 2012765681 Country of ref document: EP |
|
NENP | Non-entry into the national phase |
Ref country code: DE |