WO2017173867A1 - 一种血糖监测装置及其监测方法 - Google Patents

一种血糖监测装置及其监测方法 Download PDF

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Publication number
WO2017173867A1
WO2017173867A1 PCT/CN2017/070164 CN2017070164W WO2017173867A1 WO 2017173867 A1 WO2017173867 A1 WO 2017173867A1 CN 2017070164 W CN2017070164 W CN 2017070164W WO 2017173867 A1 WO2017173867 A1 WO 2017173867A1
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blood glucose
module
monitoring device
glucose monitoring
current
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PCT/CN2017/070164
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English (en)
French (fr)
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金海岚
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京东方科技集团股份有限公司
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Priority to US15/539,116 priority Critical patent/US20180103880A1/en
Publication of WO2017173867A1 publication Critical patent/WO2017173867A1/zh

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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
    • A61B5/14532—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
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0004—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by the type of physiological signal transmitted
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0026—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by the transmission medium
    • A61B5/0028—Body tissue as transmission medium, i.e. transmission systems where the medium is the human body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0048—Detecting, measuring or recording by applying mechanical forces or stimuli
    • 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
    • A61B5/14507—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 specially adapted for measuring characteristics of body fluids other than blood
    • 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
    • A61B5/1486—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 enzyme electrodes, e.g. with immobilised oxidase
    • 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
    • A61B5/42—Detecting, measuring or recording for evaluating the gastrointestinal, the endocrine or the exocrine systems
    • A61B5/4261—Evaluating exocrine secretion production
    • A61B5/4277—Evaluating exocrine secretion production saliva secretion
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient ; user input means
    • A61B5/746—Alarms related to a physiological condition, e.g. details of setting alarm thresholds or avoiding false alarms
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02—Operational features
    • A61B2560/0223—Operational features of calibration, e.g. protocols for calibrating sensors
    • 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
    • A61B5/1455—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 optical sensors, e.g. spectral photometrical oximeters
    • 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
    • A61B5/150748—Having means for aiding positioning of the piercing device at a location where the body is to be pierced
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7271—Specific aspects of physiological measurement analysis
    • A61B5/7275—Determining trends in physiological measurement data; Predicting development of a medical condition based on physiological measurements, e.g. determining a risk factor
    • 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 disclosure relates to the technical field of blood glucose monitoring, and in particular to a blood glucose monitoring device and a monitoring method thereof.
  • self-glycemic monitoring is currently widely recognized as a management method for diabetes in the world.
  • Self-glycemic monitoring requires patients to detect blood glucose 5-6 times a day, which is very time consuming and labor intensive.
  • a blood glucose monitoring apparatus comprising: a housing; a micro-current stimulation module that connects two electrodes and generates a current, the two electrodes are located on a surface of the housing and the current passes through the two Electrodes stimulate the user's parotid gland to produce fresh saliva; a saliva acquisition module for obtaining glucose concentration in saliva; a control processing module for controlling the micro-current stimulation module to operate, and for obtaining a glucose concentration according to the Blood glucose concentration value.
  • the blood glucose monitoring device further includes a display module, configured to display the blood glucose concentration value obtained by the control processing module.
  • the blood glucose monitoring device further includes a wireless communication module through which the control processing module communicates with an external terminal.
  • a current intensity control module is integrated in the control processing module for controlling a current intensity generated by the micro current stimulation module.
  • the blood glucose monitoring device further includes a current intensity adjustment button that is operated to pass the current intensity control module The current intensity of the micro-current stimulation module is controlled; a current intensity adjustment button may be disposed on a surface of the outer casing.
  • the control processing module is further configured to control the display module to display a current intensity level, and control the current intensity control module according to the current intensity level selected by the user. The intensity of the current generated by the microcurrent stimulation module.
  • the blood glucose monitoring device further includes a test strip detachably secured to the outer casing.
  • the test paper box comprises a box body, an elastic member disposed at a bottom of the box body, and a push rod disposed at a top of the box body; wherein the side surface of the box body is provided with a test paper near a top position An outlet; the push rod is disposed opposite the test paper outlet, and the push rod extends from the inside of the casing to outside the casing.
  • a portion of the push rod extending outside the casing is located in the outer casing and connected to the control processing module; and wherein the blood glucose monitoring device further has a test paper control button that is operated to pass through
  • the control processing module controls the pusher to eject the test paper from the test tray.
  • the control processing module is further configured to control the display module to display a test strip control button, and control the push rod to push out the test strip according to the user's selection of the test strip control button.
  • the blood glucose monitoring device further includes a power supply module through which the blood glucose monitoring device is powered.
  • a battery placement area may be disposed in the housing for placing a battery for supplying power to the power supply module; and/or a power interface is further disposed on the housing, and the external power supply passes through the power interface Powering the power supply module.
  • the blood glucose monitoring device further includes an alarm module, configured to provide an alarm signal when the control processing module determines that the blood glucose concentration value is greater than a preset threshold.
  • the material of the outer casing is a flexible material.
  • a monitoring method of the above blood glucose monitoring device comprising: after receiving an instruction of blood glucose monitoring, stimulating a user's parotid gland by a micro current to generate fresh saliva according to fresh saliva to obtain a glucose concentration; The glucose concentration is converted to a blood glucose concentration value.
  • the method further comprises: displaying the blood glucose concentration value.
  • the monitoring method further includes: sending an alarm signal when the blood glucose concentration value is greater than a preset threshold.
  • the blood glucose monitoring device and the monitoring method thereof provided by the embodiments of the present disclosure can be first passed
  • the micro-current stimulation module stimulates the user to produce fresh saliva, and then detects the glucose concentration in the fresh saliva through the saliva acquisition module.
  • the control processing module processes the acquired glucose concentration, a blood glucose concentration value can be obtained.
  • the blood glucose concentration value can also be transmitted to the external device through the wireless communication module. In this way, the effects of food residues or other substances in the oral cavity can be eliminated, and the influence of the oral environment on the measurement accuracy can be reduced, thereby improving the monitoring accuracy and reliability, and also preventing the user from having saliva without dry mouth. test.
  • FIG. 1 is a first schematic diagram of an internal structure of a blood glucose monitoring device according to an embodiment of the present disclosure
  • FIG. 2 is a second schematic diagram of an internal structure of a blood glucose monitoring device according to an embodiment of the present disclosure
  • FIG. 3 is a first schematic view of a surface of a housing of a blood glucose monitoring device according to an embodiment of the present disclosure
  • FIG. 4 is a third schematic diagram of an internal structure of a blood glucose monitoring device according to an embodiment of the present disclosure.
  • FIG. 5 is a second schematic view of a surface of a housing of a blood glucose monitoring device according to an embodiment of the present disclosure
  • FIG. 6 is a first schematic diagram of a blood glucose monitoring device including a test strip provided in accordance with an embodiment of the present disclosure
  • FIG. 7 is a schematic view showing the structure of a test paper cassette according to an embodiment of the present disclosure.
  • FIG. 8 is a second schematic diagram of a blood glucose monitoring device including a test strip provided in accordance with an embodiment of the present disclosure
  • FIG. 9 is a schematic diagram of a blood glucose monitoring device including a battery placement area, according to an embodiment of the present disclosure.
  • FIG. 10 is a schematic diagram of a blood glucose monitoring device including a power interface, according to an embodiment of the present disclosure
  • FIG. 11 is a schematic diagram of a blood glucose monitoring device including a battery placement area and a power interface, according to an embodiment of the present disclosure
  • FIG. 12 is a schematic diagram of an internal structure of a blood glucose monitoring device including an alarm module according to an embodiment of the present disclosure
  • FIG. 13 is a schematic flow chart of a monitoring method according to an embodiment of the present disclosure.
  • 10-shell 101-open; 102-switch; 103-current intensity adjustment button; 104-test paper control button; 20-microcurrent stimulation module; 201-first electrode; 202-second electrode; 30-salt acquisition module 40-control processing module; 401-current intensity control module; 50-wireless communication module; 60-display module; 70-test tray; 701-box; 702-elastic component; 703-push; 704-test paper exit ; 705 - carrier tray; 80 - test paper; 90 - battery placement area; 100 - power interface; 110 - alarm module.
  • Embodiments of the present disclosure provide a blood glucose monitoring device, as shown in FIGS. 1-2, including the following components: a housing 10, a micro-current stimulation module 20, a saliva acquisition module 30, and a control processing module 40.
  • the blood glucose monitoring device can also include a wireless communication module 50.
  • the micro-current stimulation module 20 connects two electrodes, a first electrode 201 and a second electrode 202.
  • the two electrodes are located on the surface of the outer casing 10 through which the current generated by the microcurrent stimulation module stimulates the user's parotid glands to produce fresh saliva.
  • the salvia acquisition module 30 can be used to obtain a concentration of glucose in the saliva.
  • the control processing module 40 can be configured to obtain a blood glucose concentration value based on the glucose concentration acquired by the saliva acquisition module 30; and control the micro-current stimulation module 20 to operate.
  • the control processing module 40 can communicate with an external terminal through the wireless communication module 50.
  • micro-current stimulation module the saliva acquisition module, and the control processing module described above may be implemented as a component of a processor, an integrated circuit, or a system on a chip,
  • ASIC Application Specific Integrated Circuit
  • FPGA Field Programmable Gate Array
  • CPLD Complex Programmable Logic Equipment
  • the current generated by the micro-current stimulation module 20 is a micro-current, which may be a pulsed current, or may also be a constant current.
  • the intensity of the microcurrent can be in the order of microamperes ( ⁇ A), for example, in the range of 1-500 ⁇ A.
  • two electrodes namely the first electrode 201 and the second electrode 202
  • the micro-current generated by the micro-current stimulation module 20 stimulates the parotid gland to produce fresh saliva.
  • One of the first electrode 201 and the second electrode 202 is an anode and the other is a cathode.
  • the salivary sugar acquisition module 30 can obtain the glucose concentration in the saliva using, for example, a test paper.
  • the glucose concentration here can be characterized by current or by a value of the glucose concentration obtained by converting the current value.
  • an opening 101 may be formed in the outer casing 10 of the blood glucose monitoring device, and the test paper may be inserted into the outer casing 10 to be in contact with the saliva obtaining module 30.
  • the above test paper can be used to detect glucose in saliva by an electrochemical enzyme detection method.
  • the salivary sugar acquisition module 30 acquires a current value characterizing the glucose concentration through an electrode disposed on the test paper.
  • the electrochemical enzyme detection method can be implemented based on the reaction of glucose with Glucose Oxidase (GOD) and potassium ferricyanide.
  • the glucose in the saliva is catalytically oxidized to gluconic acid by GOD on the test paper, while the GOD is converted to its reduced state. That is, the following reaction formula can be used: glucose + GOD (OX) ⁇ gluconic acid + GOD (RED) ; subscripts ox and red represent the oxidation state and the reduced state, respectively.
  • the reduced state GOD reduces the ferricyanide ions in the potassium ferricyanide to ferrocyanide ions. That is, it can be characterized by the following reaction formula: GOD (RED) + 2M (OX) ⁇ GOD (OX) + 2M (RED) + 2H + ; M (OX) and M (RED) represent ferricyanide and ferrous, respectively Cyanide ion.
  • the ferrocyanide ions When a certain voltage is applied to the test paper, the ferrocyanide ions are reduced to ferricyanide ions, and an electric current is generated. That is, it can be characterized by the following reaction formula: 2M (RED) ⁇ 2M (OX) + 2e - ; e - represents an electron. The greater the number of free electrons produced, the greater the current, which is proportional to the glucose concentration.
  • the control processing module 40 can convert the glucose concentration acquired by the saliva obtaining module 30 into a blood glucose concentration value.
  • the control processing module 40 can control the micro-current stimulation module 20 to operate.
  • a switch 102 may be provided on the surface of the outer casing 10. Normally, the switch 102 can be turned to the ON state by default to use the blood glucose monitoring device.
  • the micro-current stimulation module 20 is controlled by the control processing module 40 to operate. When the user does not need the micro-current stimulation module 20 to generate a stimulation current, the switch 102 can be turned to the OFF state so that the control processing module 40 does not control the micro-current stimulation module 20 to operate.
  • the wireless communication module 50 can be Bluetooth, wifi, or the like. Through the wireless communication module 50, the control processing module 40 can transmit the blood glucose concentration value to the external device.
  • the external device can be a mobile phone, a computer, or the like, or a server.
  • the blood glucose concentration value obtained by each measurement can be stored by the peripheral device for management.
  • the outer casing 10 needs to be in contact with the human body, the material thereof needs to be non-toxic and wear resistant.
  • Embodiments of the present disclosure provide a blood glucose monitoring device that can generate fresh saliva by stimulating the user's parotid gland by the micro-current stimulation module 20. Therefore, the influence of food residue or other substances in the oral cavity can be excluded, the influence of the oral environment on the measurement accuracy is reduced, thereby improving the monitoring accuracy and reliability, and also avoiding the fact that the user does not have saliva when the mouth is dry and cannot be tested.
  • the blood glucose monitoring device further includes a display module 60 configured to display the blood glucose concentration value obtained by the control processing module 40.
  • the display module 60 can be any type of display, for example, a liquid crystal display (LCD), an OLED (Organic Light-Emitting Diode, OLED) display, or the like.
  • LCD liquid crystal display
  • OLED Organic Light-Emitting Diode
  • the display module 60 may further have a touch function.
  • the display module 60 in order to adapt the blood glucose monitoring device to different user requirements, in addition to displaying the blood glucose concentration value on the display interface of the display, it can also be displayed on the display interface of the display for closing under the control of the control processing module 40.
  • the button identification of the micro current stimulation module 20 Normally, the micro-current stimulation module 20 can be turned on by default to control the micro-current stimulation module 20 to operate by the control processing module 40 when the blood glucose monitoring device is used.
  • the user can select the button identifier for turning off the micro-current stimulation module 20 on the display interface by touch control, so that the control processing module 40 does not control the micro-current stimulation module 20 to work. .
  • an identifier for selecting whether the display module 60 is working or whether the wireless communication module 50 is working may be displayed on the display interface of the display to improve the user experience.
  • the display surface of the display module 60 may be flush with the outer casing 10 or protrude from the outer casing 10.
  • the wireless communication module 50 can be disposed within the housing 10 or can be embedded in the housing 10.
  • a current intensity control module 401 is integrated in the control processing module 40 for controlling the current intensity generated by the micro current stimulation module 20.
  • a current intensity adjustment button 103 may be disposed on the surface of the outer casing 10 for controlling the current intensity generated by the micro current stimulation module 20 by the current intensity control module 401.
  • the current intensity can be set to several levels, for example, as shown in FIG. 5, five levels are set, and the levels are in one-to-one correspondence with a plurality of current intensities. As the level increases, the current intensity also increases. In this way, according to the needs of the user, the appropriate current intensity can be selected for stimulation to improve the user experience.
  • the control processing module 40 can also be used to control the display module 60 to display the level of the current intensity, and according to the level of the current intensity selected by the user,
  • the current intensity control module 401 controls the current intensity generated by the micro current stimulation module 20.
  • the display module 60 can display, for example, five levels.
  • the current intensity control module 401 can control the micro current stimulation module 20 to generate a corresponding current intensity.
  • the blood glucose monitoring device further includes a test paper cassette 70 that is detachably fixed to the outer casing 10.
  • the test paper cassette 70 can be placed in a spit sugar monitoring device, which facilitates carrying the test paper conveniently. Moreover, since the test paper cassette is detachable, the test paper cassette 70 can be easily replaced after the test paper in the test paper 70 is used up.
  • the test paper cassette 70 includes a case body 701, an elastic member 702 disposed at the bottom of the case body, and a push rod 703 disposed at the top of the case body.
  • a test paper exit 704 is disposed at a side of the casing 701 near the top position; a push rod 703 is disposed opposite the test paper exit 704, and the push rod 703 extends from the inside of the casing to the outside of the casing.
  • test paper cassette 70 The working principle of the test paper cassette in the embodiment of the present disclosure is that when the test paper 80 is filled with the test paper cassette 70, the elastic member 702 is in a compressed state; by controlling the push rod 703, it can be located in the box
  • the test paper 80 at the top of the body 701 is pushed out from the test paper exit 704.
  • the pressure applied to the elastic member 702 is reduced and gradually extended to push the test paper 80 located above the upper portion to the top of the casing 701 so as to be pushed by the push rod 703. It is launched from the test paper exit 704. Subsequent test strips 80 are introduced in a similar manner.
  • the resilient member 702 can be, for example, a spring.
  • a carrier disk 705 may be fixed over the elastic member 702.
  • test paper exit 704 it is necessary to expose the test paper exit 704 to the outer casing 10 after the test paper cassette 70 is loaded into the blood glucose monitoring device.
  • the pusher 703 the automatic ejection of the test strip 80 can be achieved.
  • a portion of the push rod 703 that extends outside the casing 701 may be located within the outer casing 10 and coupled to the control processing module 40.
  • a test paper control button 104 is further disposed on the surface of the outer casing 10 for controlling the push rod 703 to eject the test paper 80 from the test paper 70 by the control processing module 40.
  • the control processing module 40 can control the pusher 703 to eject a test strip 80 from the test paper 70, and then the test paper control button 104 can be Dial from the ON state to the OFF state. As long as the control processing module 40 detects that the test paper control button 104 is turned from the OFF state to the ON state, the pusher 703 can be controlled to push out a test strip 80. This significantly improves the user experience.
  • the control processing module 40 can also be used to control the display module 60 to display the test paper control button, and according to the user selection, the control push rod 703 is pushed out. Test strip 80.
  • a power supply module (not shown) is required in the blood glucose monitoring device.
  • a battery placement area 90 is further disposed in the casing 10 for placing a battery for supplying power to the power supply module.
  • a power interface 100 is also provided on the housing 10 that can be connected to an external power source for powering the power supply module.
  • a battery placement area 90 is provided in the casing 10, and a power supply interface 100 is also provided on the casing 10.
  • the blood glucose monitoring device further includes an alarm module 110, configured to provide an alarm signal when the control processing module 40 determines that the blood glucose concentration value is greater than a preset threshold.
  • the alarm module 110 can be an alarm function for a buzzer, a light emitting diode, or the like. Device.
  • the alarm module 110 may be disposed within the outer casing 10, or embedded in the outer casing 10, or disposed on an outer surface of the outer casing 10.
  • the user when the blood glucose concentration value is relatively high, the user can know his or her physical condition in time.
  • the material of the outer casing 10 is a flexible material.
  • the material of the outer casing 10 is a flexible material.
  • the material of the outer casing 10 may be silica gel. This is because the silicone is softer and does not irritate the user's skin.
  • An embodiment of the present disclosure further provides a monitoring method of a blood glucose monitoring device, as shown in FIG. 13, comprising the following steps:
  • the instructions can be controlled by the user.
  • a power switch can be disposed on the blood glucose monitoring device.
  • the control processing module 40 receiving the blood glucose monitoring command.
  • the micro-current stimulation module 20 can generate a pulsed current or can also generate a constant current.
  • the microcurrent intensity can be in the order of microamperes ( ⁇ A), for example, in the range of 1-500 ⁇ A.
  • the two electrodes ie, the first electrode 201 and the second electrode 202
  • the two electrodes may be in contact with the skin at the parotid gland.
  • the micro-current generated by the micro-current stimulation module 20 stimulates the parotid gland to produce fresh saliva.
  • the glucose concentration in the saliva can be obtained here by the salvia obtaining module 30, wherein the glucose concentration can be characterized by current, or can be a glucose concentration value obtained by converting the current value.
  • S12 Converting the glucose concentration into a blood glucose concentration value.
  • the glucose concentration value can be converted to a blood glucose concentration value by the control processing module 40. There is a linear relationship between blood glucose concentration y and glucose concentration x. Additionally, the blood glucose concentration value can be sent to an external device for ease of management and storage.
  • the monitoring method further comprises: displaying the blood glucose concentration value.
  • control processing module 40 controls the display module 60 to display the blood glucose concentration value.
  • the monitoring method further includes: issuing an alarm when the blood glucose concentration value is greater than a preset threshold.
  • the alarm module 110 can be controlled to provide an alarm signal.
  • the foregoing program may be stored in a computer readable storage medium, and the program is executed when executed.
  • the foregoing steps include the steps of the foregoing method embodiments; and the foregoing storage medium includes: a medium that can store program codes, such as a ROM, a RAM, a magnetic disk, or an optical disk.

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  • Measuring And Recording Apparatus For Diagnosis (AREA)

Abstract

一种血糖监测装置及其监测方法，可减小口腔环境对测量准确度的影响。该血糖监测装置包括：外壳(10)；微电流刺激模块(20)，其连接两个电极(201,202)并且产生电流，所述两个电极(201,202)位于所述外壳(10)表面并且所述电流通过所述两个电极(201,202)刺激用户的腮腺以产生新鲜唾液；唾糖获取模块(30)，用于获取唾液中的葡萄糖浓度；控制处理模块(40)，用于控制所述微电流刺激模块(20)进行工作，以及用于根据所述葡萄糖浓度得到血糖浓度值。

Description

一种血糖监测装置及其监测方法
相关申请
本PCT申请要求申请日为2016年4月5日、申请号为NO.201610207628.8的中国专利申请的优先权，该优先权申请的整体内容通过引用的方式被合并于此。
技术领域
本公开涉及血糖监测的技术领域，尤其涉及一种血糖监测装置及其监测方法。
背景技术
随着现代人类劳动强度显著下降和饮食习惯的改变，糖尿病的发病率迅速上升，糖尿病及其并发症所造成的影响已成为世界各国均需面对的严重的公共卫生问题之一。
目前，自我血糖监测是目前国际广泛认可的糖尿病管理办法。而自我血糖监测需要患者每天检测5-6次血糖，这非常耗时耗力。
发明内容
根据本公开的一个方面，提供一种血糖监测装置，包括：外壳；微电流刺激模块，其连接两个电极并且产生电流，所述两个电极位于所述外壳表面并且所述电流通过所述两个电极刺激用户的腮腺以产生新鲜唾液；唾糖获取模块，用于获取唾液中的葡萄糖浓度；控制处理模块，用于控制所述微电流刺激模块进行工作，以及用于根据所述葡萄糖浓度得到血糖浓度值。。
可选地，所述血糖监测装置还包括显示模块，用于将所述控制处理模块得到的所述血糖浓度值进行显示。
可选地，所述的血糖监测装置还包括无线通信模块，所述控制处理模块通过其与外部终端进行通信。
可选地，所述控制处理模块中集成有电流强度控制模块，用于控制所述微电流刺激模块产生的电流强度。作为示例，所述血糖监测装置还包括电流强度调节按钮，其被操作来通过所述电流强度控制模块 控制所述微电流刺激模块的电流强度；电流强度调节按钮可以设置在所述外壳的表面。或者，在所述显示模块具有触控功能的情况下，所述控制处理模块还可用于控制所述显示模块显示电流强度等级，并根据用户选择的电流强度等级，通过所述电流强度控制模块控制所述微电流刺激模块产生的电流强度。
可选地，所述血糖监测装置还包括以可拆卸方式固定在所述外壳上的试纸盒。
可选地，所述试纸盒包括盒体、设置在所述盒体底部的弹性部件以及设置在所述盒体顶部的推杆；其中，所述盒体的侧面靠近顶部位置处设置有试纸出口；所述推杆与所述试纸出口相对设置，且所述推杆从所述盒体内延伸到所述盒体外。
可选地，所述推杆的延伸到所述盒体外侧的部分位于所述外壳内，并与所述控制处理模块连接；并且其中血糖监测装置还具有试纸控制按钮，其被操作来通过所述控制处理模块控制所述推杆以便从所述试纸盒中推出试纸。或者，在所述显示模块具有触控功能的情况下，所述控制处理模块还用于控制所述显示模块显示试纸控制按钮，并根据用户对试纸控制按钮的选择，控制所述推杆推出试纸。
可选地，所述血糖监测装置还包括供电模块，通过其向所述血糖监测装置供电。在所述外壳内还可设置有电池放置区，用于放置电池，该电池用于向所述供电模块供电；和/或，在所述外壳上还设置有电源接口，外部电源通过该电源接口向所述供电模块供电。
可选地，所述血糖监测装置还包括告警模块，用于在所述控制处理模块判断所述血糖浓度值大与预设阈值时，提供告警信号。
可选地，所述外壳的材料为柔性材料。
根据本公开的另一方面，提供了一种上述血糖监测装置的监测方法，包括：接收到血糖监测的指令后，由微电流刺激用户的腮腺，产生新鲜唾液根据新鲜唾液，得到葡萄糖浓度；将葡萄糖浓度换算为血糖浓度值。
可选地，所述方法还包括：显示所述血糖浓度值。
可选地，所述监测方法还包括：当所述血糖浓度值大与预设阈值时，发出告警信号。
采用本公开的实施例提供的血糖监测装置及其监测方法，可先通 过微电流刺激模块刺激用户产生新鲜唾液，然后通过唾糖获取模块对新鲜唾液中的葡萄糖浓度进行检测。在控制处理模块将获取的所述葡萄糖浓度处理后，可以得到血糖浓度值。之后，还可通过无线通信模块将所述血糖浓度值发送到外部设备。以这种方式，可排除口腔内食物残渣或其他物质造成的影响，减小口腔环境对测量准确度的影响，从而提高了监测精度与可靠性，也可避免用户口干时没有唾液而无法进行测试。
附图说明
为了更清楚地说明本公开的实施例，下面将对描述实施例中所需要使用的附图作简单的介绍。下面描述中的附图仅仅是本公开的一些实施例。对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他的附图。
图1为根据本公开的实施例提供的一种血糖监测装置的内部结构的第一示意图；
图2为根据本公开的实施例提供的一种血糖监测装置的内部结构的第二示意图；
图3为根据本公开的实施例提供的一种血糖监测装置的外壳表面的第一示意图；
图4为根据本公开的实施例提供的一种血糖监测装置的内部结构的第三示意图；
图5为根据本公开的实施例提供的一种血糖监测装置的外壳表面的第二示意图；
图6为根据本公开的实施例提供的一种包括试纸盒的血糖监测装置的第一示意图；
图7为根据本公开的实施例提供的一种试纸盒的结构的示意图；
图8为根据本公开的实施例提供的一种包括试纸盒的血糖监测装置的第二示意图；
图9为根据本公开的实施例提供的一种包括电池放置区的血糖监测装置的示意图；
图10为根据本公开的实施例提供的一种包括电源接口的血糖监测装置的示意图；
图11为根据本公开的实施例提供的一种包括电池放置区和电源接口的血糖监测装置的示意图；
图12为根据本公开的实施例提供的一种包括告警模块的血糖监测装置的内部结构的示意图；
图13为根据本公开的实施例提供的一种监测方法的流程示意图。
附图标记：
10-外壳；101-开口；102-开关；103-电流强度调节按钮；104-试纸控制按钮；20-微电流刺激模块；201-第一电极；202-第二电极；30-唾糖获取模块；40-控制处理模块；401-电流强度控制模块；50-无线通信模块；60-显示模块；70-试纸盒；701-盒体；702-弹性部件；703-推杆；704-试纸出口；705-承载盘；80-试纸；90-电池放置区；100-电源接口；110-告警模块。
具体实施方式
下面将结合附图，对本公开的实施例中的技术方案进行清楚、完整的描述。显然，所描述的实施例仅仅是本公开的一部分实施例，而不是全部的实施例。基于本公开中的实施例，本领域普通技术人员在没有做出创造性劳动前提下所获得的所有其他实施例，都属于本公开保护的范围。
本公开的实施例提供了一种血糖监测装置，如图1-2所示，包括如下部件：外壳10，微电流刺激模块20，唾糖获取模块30，控制处理模块40。所述血糖监测装置还可以包括无线通信模块50。
微电流刺激模块20连接两个电极，即第一电极201和第二电极202。该两个电极位于外壳10表面，微电流刺激模块产生的电流通过该两个电极刺激用户的腮腺，以产生新鲜唾液。
唾糖获取模块30可以用于获取唾液中的葡萄糖浓度。
控制处理模块40可以用于根据唾糖获取模块30获取的葡萄糖浓度得到血糖浓度值；以及控制微电流刺激模块20进行工作。
控制处理模块40可以通过无线通信模块50与外部终端进行通信。
应当指出，上述微电流刺激模块、唾糖获取模块、控制处理模块中的一个或多个可以被实施为处理器、集成电路或片上系统的构件、
专用集成电路(ASIC)、现场可编程门阵列(FPGA)、复杂可编程逻 辑器件(CPLD)等等。
在本公开的实施例中，微电流刺激模块20产生的电流是微电流，所述微电流可以是脉冲电流，或者也可以是恒流。微电流的强度可在微安(μA)级，例如可以为1-500μA范围内。
当使用本公开的血糖监测装置时，可将两个电极，即第一电极201和第二电极202，与腮腺处的皮肤接触，由微电流刺激模块20产生的微电流刺激腮腺而产生新鲜唾液。第一电极201和第二电极202中的一个为阳极，另一个为阴极。
唾糖获取模块30例如可利用试纸得到唾液中的葡萄糖浓度。此处的葡萄糖浓度可以以电流方式进行表征，或者是将电流值换算得到的葡萄糖浓度值。如图3所示，血糖监测装置的外壳10上可设置开口101，通过该开口101，可将试纸插入外壳10内部而与唾糖获取模块30接触。
上述的试纸可采用电化学酶检测方法检测唾液中的葡萄糖。唾糖获取模块30通过设置在试纸上的电极，获取表征葡萄糖浓度的电流值。
作为一个示例，电化学酶检测方法可是基于葡萄糖与葡萄糖氧化酶(Glucose Oxidase，简称GOD)和铁氰化钾反应来实现的。
唾液中的葡萄糖经试纸上的GOD催化氧化为葡萄糖酸，同时GOD转化为其还原态。即，可以采用下述反应式表征：葡萄糖+GOD(OX)→葡萄糖酸+GOD(RED)；下标ox和red分别代表氧化态与还原态。
接着，还原态的GOD将铁氰化钾中的铁氰离子还原为亚铁氰离子。即，可以采用下述反应式表征：GOD(RED)+2M(OX)→GOD(OX)+2M(RED)+2H+；M(OX)和M(RED)分别代表铁氰离子和亚铁氰离子。
当向试纸施加一定的电压后，亚铁氰离子还原为铁氰离子，并产生电流。即，可以采用下述反应式表征：2M(RED)→2M(OX)+2e-；e-代表电子。产生的自由电子数目越多，电流也越大，电流大小与葡萄糖浓度成正比。
控制处理模块40可将唾糖获取模块30获取的葡萄糖浓度换算成血糖浓度值。血糖浓度y与葡萄糖浓度x存在如下的线性关系，即，y＝a×x+b，其中a和b可预先获取并存储。另一方面，控制处理模块40可控制微电流刺激模块20进行工作。为了使该血糖监测装置适用不同的用户需求，例如如图3所示，可在外壳10表面设置开关102。通常情况下，可默认将开关102拨到ON状态，以在使用该血糖监测装置 时，由控制处理模块40控制微电流刺激模块20进行工作。当用户不需要微电流刺激模块20产生刺激电流时，则可将开关102拨到OFF状态，以使控制处理模块40不控制微电流刺激模块20进行工作。
无线通信模块50可以是蓝牙、wifi等。通过无线通信模块50，控制处理模块40可将血糖浓度值发送到外部设备。外部设备可以是手机、电脑等，也可以是服务器。
在此情况下，通过外围设备可以把每次测量得到的血糖浓度值进行存储，便于管理。
需要说明的是，由于外壳10需要与人体接触，因此其材料需为无毒，且为耐磨损材料。
本公开的实施例提供了一种血糖监测装置，其可通过微电流刺激模块20刺激用户的腮腺而产生新鲜的唾液。因此，可排除口腔内食物残渣或其他物质的影响，减小了口腔环境对测量准确度的影响，从而提高了监测精度与可靠性，也可避免用户口干时没有唾液而无法进行测试。
可选地，如图2所示，所述血糖监测装置还包括显示模块60，用于将控制处理模块40得到的所述血糖浓度值进行显示。
此处，显示模块60可以是任意类型的显示器，例如可以是液晶显示器(Liquid Crystal Display，简称LCD)、OLED(Organic Light-Emitting Diode，简称OLED)显示器等。
进一步地，上述显示模块60还可以具有触控功能。在此基础上，为了使该血糖监测装置适用不同的用户需求，除了在显示器的显示界面显示血糖浓度值外，还可以在控制处理模块40的控制下，在显示器的显示界面上显示用于关闭微电流刺激模块20的按钮标识。通常情况下，可默认微电流刺激模块20为开启状态，以在使用该血糖监测装置时，由控制处理模块40控制微电流刺激模块20进行工作。当用户不需要微电流刺激模块20产生刺激时，用户可通过触控方式在显示界面选择用于关闭微电流刺激模块20的按钮标识，以使控制处理模块40不控制微电流刺激模块20进行工作。
此外，还可在控制处理模块40的控制下，在显示器的显示界面显示用于选择显示模块60是否工作，或选择无线通信模块50是否工作的标识，以提高用户体验。
需要说明的是，显示模块60的显示面可以与外壳10齐平，或突出于外壳10。无线通信模块50可设置在外壳10内，也可嵌在外壳10上。
可选地，如图4所示，控制处理模块40中集成有电流强度控制模块401，用于控制微电流刺激模块20产生的电流强度。
在此基础上，如图5所示，在外壳10的表面还可设置电流强度调节按钮103，用于通过电流强度控制模块401控制微电流刺激模块20产生的电流强度。
此处，可将电流强度设为几个等级，例如如图5所示，设置5个等级，并将所述等级与多个电流强度一一对应。随着等级的升高，电流强度也逐渐加大。这样，可根据用户的需求，选择适合的电流强度进行刺激，提高用户体验。
需要说明的是，本公开的实施例并不限于是5个等级，等级的数量可根据实际情况被具体设置。
当所述血糖监测装置还包括显示模块60且显示模块60具有触控功能时，控制处理模块40还可以用于控制显示模块60显示电流强度的等级，并根据用户选择的电流强度的等级，通过电流强度控制模块401来控制微电流刺激模块20产生的电流强度。
与上述电流强度调节按钮103的功能类似，显示模块60可以显示例如5个等级。当用户选择相应的等级后，电流强度控制模块401便可控制微电流刺激模块20产生相应的电流强度。
可选地，如图6所示，所述血糖监测装置还包括以可拆卸方式固定在外壳10上的试纸盒70。
在本公开的实施例中，可以将试纸盒70设置在唾糖监测装置中，这有利于方便携带试纸。而且，由于试纸盒是可拆卸的，所以当试纸盒70中的试纸用完后，试纸盒70可方便地被更换。
进一步可选地，如图6-7所示，试纸盒70包括盒体701、设置在盒体底部的弹性部件702以及设置在盒体顶部的推杆703。
盒体701的侧面靠近顶部位置处设置有试纸出口704；推杆703与试纸出口704相对设置，且推杆703从盒体内延伸到盒体外。
本公开的实施例中的试纸盒的工作原理为：当试纸80装满试纸盒70时，弹性部件702处于压缩状态；通过控制推杆703，可将位于盒 体701最上方的试纸80从试纸出口704推出。在此过程中，由于弹性部件702上方的试纸80减少，弹性部件702受到的压力减小，逐渐伸展，以将位于次上方的试纸80推到盒体701的顶部，以便通过推杆703将其从试纸出口704推出。后续试纸80以类似方式被推出。
弹性部件702例如可以为弹簧。为了避免弹性部件702与试纸80接触时，损伤试纸80，可以在弹性部件702上方固定一承载盘705。
需要说明的是，对于试纸出口704的设置位置而言，需能在试纸盒70装入血糖监测装置后，在外壳10上露出试纸出口704。这样，通过控制推杆703，便可实现试纸80的自动推出。
可选地，推杆703的延伸到盒体701外侧的部分可以位于外壳10内，并与控制处理模块40连接。在此基础上，可选地，如图8所示，在外壳10的表面还设置有试纸控制按钮104，用于通过控制处理模块40控制推杆703从试纸盒70中推出试纸80。
如图8所示，当将试纸控制按钮104从OFF状态拨到ON状态时，控制处理模块40便可控制推杆703从试纸盒70中推出一张试纸80，之后可将试纸控制按钮104从ON状态拨到OFF状态。只要控制处理模块40检测到试纸控制按钮104从OFF状态拨到ON状态，就可控制推杆703推出一张试纸80。这显著提高了用户体验。
当然，当所述血糖监测装置还包括显示模块60，且显示模块60具有触控功能时，控制处理模块40还可用于控制显示模块60显示试纸控制按钮，并根据用户选择，控制推杆703推出试纸80。
由于血糖监测装置要实现正常工作，必须要对各模块进行供电，因此在血糖监测装置中需有供电模块(图中未标识出)。在此基础上，如图9所示，在外壳10内还设置有电池放置区90，用于放置电池，该电池用于向供电模块供电。或者，如图10所示，在外壳10上还设置有电源接口100，其可以连接到外部电源以用于向供电模块供电。或者，如图11所示，在外壳10内设置电池放置区90的同时，还在外壳10上设置有电源接口100。
可选地，如图12所示，所述血糖监测装置还包括告警模块110，用于在控制处理模块40判断所述血糖浓度值大与预设阈值时，提供告警信号。
此处，告警模块110可以为蜂鸣器、发光二极管等具有告警功能 的器件。告警模块110可以设置在外壳10内，或嵌入外壳10，或设置在外壳10外表面。
在本公开的实施例中，当血糖浓度值比较高时，用户可以及时知道自身身体状况。
可选地，外壳10的材料为柔性材料。这样，在血糖监测装置与用户皮肤接触以刺激用户的腮腺产生新鲜唾液的过程中，避免了由于外壳10材料的原因而导致用户不舒服。
可选地，外壳10的材料可以为硅胶。这是由于硅胶较为柔软，不会刺激用户皮肤。
本公开的实施例还提供了一种血糖监测装置的监测方法，如图13所示，包括如下步骤：
S10：接收到血糖监测的指令后，由微电流刺激用户的腮腺，产生新鲜唾液。
此处，指令可由用户控制。以上述的血糖监测装置为例，可在血糖监测装置上设置一个电源开关，当用户控制电源开关开启时，相当于控制处理模块40接收到血糖监测的指令。
微电流刺激模块20可产生脉冲电流，或者也可产生恒流。微电流强度可在微安(μA)级，例如可以为1-500μA范围内。
当使用本公开中的血糖监测装置时，可将两个电极(即第一电极201和第二电极202)与腮腺处的皮肤接触。由微电流刺激模块20产生的微电流刺激腮腺而产生新鲜唾液。
S11：根据新鲜唾液，得到葡萄糖浓度。
仍以上述的血糖监测装置为例，此处可通过唾糖获取模块30得到唾液中的葡萄糖浓度，其中，葡萄糖浓度可以以电流方式进行表征，或者可以是电流值换算得到的葡萄糖浓度值。
S12：将葡萄糖浓度换算为血糖浓度值。可通过控制处理模块40将葡萄糖浓度值换算成血糖浓度值。其中血糖浓度y与葡萄糖浓度x存在线性关系。此外，可以将所述血糖浓度值发送到外部设备，以方便管理和存储。
采用本公开的实施例提供的监测方法，由于可通过微电流刺激用户的腮腺而产生新鲜的唾液，因此，可排除口腔内食物残渣或其他物质的影响，减小了口腔环境对测量准确度的影响，从而提高了监测精 度与可靠性，也可避免用户口干时没有唾液而无法进行测试。
可选地，所述监测方法还包括：显示所述血糖浓度值。
以上述的血糖监测装置为例，控制处理模块40控制显示模块60显示所述血糖浓度值。
可选地，所述监测方法还包括：当所述血糖浓度值大与预设阈值时，发出告警。
以上述的血糖监测装置为例，在控制处理模块40判断血糖浓度值大与预设阈值时，可控制告警模块110提供告警信号。
本领域普通技术人员可以理解：实现上述方法实施例的全部或部分步骤可以通过程序指令相关的硬件来完成，前述的程序可以存储于一计算机可读取存储介质中，该程序在执行时，执行包括上述方法实施例的步骤；而前述的存储介质包括：ROM、RAM、磁碟或者光盘等各种可以存储程序代码的介质。
以上所述实施例仅为本发明的示例性实施例，但本发明的保护范围并不局限于此。任何熟悉本技术领域的技术人员在本发明揭露的技术范围内，可轻易想到各种变化或替换，它们都应涵盖在本发明的保护范围之内。因此，本发明的保护范围应由所附权利要求限定。

Claims (16)

  1. 一种血糖监测装置，包括：
    外壳；
    微电流刺激模块，其连接两个电极并且产生电流，所述两个电极位于所述外壳表面并且所述电流通过所述两个电极刺激用户的腮腺以产生新鲜唾液；
    唾糖获取模块，用于获取唾液中的葡萄糖浓度；
    控制处理模块，用于控制所述微电流刺激模块进行工作，以及用于根据所述葡萄糖浓度得到血糖浓度值。
  2. 根据权利要求1所述的血糖监测装置，还包括显示模块，用于将所述控制处理模块得到的所述血糖浓度值进行显示。
  3. 根据权利要求1所述的血糖监测装置，还包括无线通信模块，所述控制处理模块通过其与外部终端进行通信。
  4. 根据权利要求1所述的血糖监测装置，其中，所述控制处理模块中集成有电流强度控制模块，用于控制所述微电流刺激模块产生的电流强度。
  5. 根据权利要求4所述的血糖监测装置，还包括电流强度调节按钮，其被操作来通过所述电流强度控制模块控制所述微电流刺激模块的电流强度。
  6. 根据权利要求1所述的血糖监测装置，还包括以可拆卸方式固定在所述外壳上的试纸盒。
  7. 根据权利要求6所述的血糖监测装置，其中，所述试纸盒包括盒体、设置在所述盒体底部的弹性部件以及设置在所述盒体顶部的推杆；
    其中，所述盒体的侧面靠近顶部位置处设置有试纸出口；
    所述推杆与所述试纸出口相对设置，且所述推杆从所述盒体内延伸到所述盒体外。
  8. 根据权利要求7所述的血糖监测装置，其中，所述推杆的延伸到所述盒体外侧的部分位于所述外壳内，并与所述控制处理模块连接；并且其中血糖监测装置还具有试纸控制按钮，其被操作来通过所述控制处理模块控制所述推杆以便从所述试纸盒中推出试纸。
  9. 根据权利要求1所述的血糖监测装置，还包括供电模块，通过其向所述血糖监测装置供电。
  10. 根据权利要求9所述的血糖监测装置，其中在所述外壳内还设置有电池放置区，用于放置电池，该电池用于向所述供电模块供电。
  11. 根据权利要求9或10所述的血糖监测装置，其中在所述外壳上还设置有电源接口，外部电源通过该电源接口向所述供电模块供电。
  12. 根据权利要求1所述的血糖监测装置，还包括告警模块，用于在所述控制处理模块判断所述血糖浓度值大与预设阈值时，提供告警信号。
  13. 根据权利要求1所述的血糖监测装置，其中，所述外壳的材料为柔性材料。
  14. 一种血糖监测装置的监测方法，包括：
    接收到血糖监测的指令后，由微电流刺激用户的腮腺，产生新鲜唾液；
    根据新鲜唾液，得到葡萄糖浓度；
    将葡萄糖浓度换算为血糖浓度值。
  15. 根据权利要求14所述的监测方法，还包括：显示所述血糖浓度值。
  16. 根据权利要求14所述的监测方法，还包括：当所述血糖浓度值大与预设阈值时，发出告警信号。
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