WO2023216800A1 - 节能分析物检测系统 - Google Patents

节能分析物检测系统 Download PDF

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Publication number
WO2023216800A1
WO2023216800A1 PCT/CN2023/088036 CN2023088036W WO2023216800A1 WO 2023216800 A1 WO2023216800 A1 WO 2023216800A1 CN 2023088036 W CN2023088036 W CN 2023088036W WO 2023216800 A1 WO2023216800 A1 WO 2023216800A1
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WO
WIPO (PCT)
Prior art keywords
analyte detection
detection device
module
signal
present
Prior art date
Application number
PCT/CN2023/088036
Other languages
English (en)
French (fr)
Inventor
杨翠军
Original Assignee
上海移宇科技有限公司
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Filing date
Publication date
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Publication of WO2023216800A1 publication Critical patent/WO2023216800A1/zh

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Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q1/00—Details of, or arrangements associated with, antennas
    • H01Q1/36—Structural form of radiating elements, e.g. cone, spiral, umbrella; Particular materials used therewith
    • 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
    • A61B5/1459—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 invasive, e.g. introduced into the body by a catheter
    • 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
    • A61B5/145—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
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q1/00—Details of, or arrangements associated with, antennas
    • H01Q1/12—Supports; Mounting means
    • H01Q1/22—Supports; Mounting means by structural association with other equipment or articles
    • H01Q1/24—Supports; Mounting means by structural association with other equipment or articles with receiving set
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02D—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN INFORMATION AND COMMUNICATION TECHNOLOGIES [ICT], I.E. INFORMATION AND COMMUNICATION TECHNOLOGIES AIMING AT THE REDUCTION OF THEIR OWN ENERGY USE
    • Y02D30/00—Reducing energy consumption in communication networks
    • Y02D30/70—Reducing energy consumption in communication networks in wireless communication networks
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02E—REDUCTION OF GREENHOUSE GAS [GHG] EMISSIONS, RELATED TO ENERGY GENERATION, TRANSMISSION OR DISTRIBUTION
    • Y02E60/00—Enabling technologies; Technologies with a potential or indirect contribution to GHG emissions mitigation
    • Y02E60/10—Energy storage using batteries

Definitions

  • the present invention mainly relates to the field of medical devices, and in particular to an energy-saving analyte detection system.
  • the pancreas in a normal human body can automatically detect the glucose content in the human blood and automatically secrete the required insulin/glucagon.
  • the function of the pancreas is abnormal and it cannot secrete the insulin that the body needs normally. Therefore, diabetes is a metabolic disease caused by abnormal pancreatic function in the human body. Diabetes is a lifelong disease. At present, medical technology cannot cure diabetes. The occurrence and development of diabetes and its complications can only be controlled by stabilizing blood sugar.
  • CGM Continuous Glucose Monitoring
  • the battery placed in it will not be too large, so the battery capacity will not be too large.
  • the battery life needs to be considered.
  • Existing analyte detection devices Signals are emitted to the outside world after leaving the factory. When users use them, the handheld device searches for these broadcast signals to complete pairing and establish a communication connection. This method of transmitting signals immediately after leaving the factory consumes too much battery energy and is difficult to meet the needs of analytes. The detection device needs to be used for a long time.
  • the invention discloses an energy-saving analyte detection system. Before the analyte detection device is installed, the processor is powered on but in a deep sleep state, and the transmitter does not transmit signals outward. After the analyte detection device is installed, it is triggered by predetermined conditions. , the processor transitions to the working state, and the transmitter begins to transmit to the outside world. Emitting signals can save battery energy consumption and extend the service life of the analyte detection device.
  • An embodiment of the present invention discloses an analyte detection device, which includes: an auxiliary installer for installing the analyte detection device on the user's skin surface; the analyte detection device at least includes a transmitter and a sensor, and the transmitter at least includes a battery, The wake-up module and the working module, the wake-up module electrically connects the battery and the working module; wherein the wake-up module at least includes a processor, a state switching component and a field effect transistor; wherein the state switching component is open circuit before triggering, and the processor is powered on and in In the deep sleep state, the field effect transistor is opened, and the battery does not provide power to the working module; after the state switching component is triggered, it is closed circuit, the processor is converted to the working state, and the field effect transistor is closed, and the battery provides power to the working module. ; Among them, after the processor is converted to the working state, the field effect transistor is locked into a closed circuit so that the battery can continue to provide power to the working module.
  • the state switching component is one of a photosensitive element, a magnetic sensing element, a touch switch or an acceleration sensor;
  • the state switching member is a photodiode.
  • the auxiliary installer is also used to provide a stable environment for the analyte detection device to prevent the state switching member from being triggered before use.
  • the auxiliary installer provides a light-shielded environment for the analyte detection device.
  • the auxiliary installer no longer provides a light-shielding environment for the analyte detection device, and the state switching component is triggered.
  • the working module at least includes an antenna.
  • the antenna transmits a signal to the outside world at a first frequency or a first signal strength.
  • the senor is a glucose sensor.
  • the processor of the wake-up module in the analyte detection device before using the auxiliary installer, the processor of the wake-up module in the analyte detection device is powered on but in a deep sleep state, and the transmitter does not transmit signals outward.
  • the wake-up module wakes up The state switching component in the module is triggered, the processor is converted to the working state, and the transmitter emits a signal outward, which can save battery energy consumption before the analyte detection device is officially used and extend the service life of the analyte detection device.
  • the field effect transistor can be locked into a closed-circuit state, and the working module can be continuously provided with power regardless of the state of the state switching component.
  • Figure 1 is a schematic structural diagram of an analyte detection system according to an embodiment of the present invention
  • Figure 2 is a schematic structural diagram of an analyte detection device according to an embodiment of the present invention.
  • Figure 3a is a schematic structural diagram of a wake-up module of an analyte detection device including a photosensitive element according to an embodiment of the present invention
  • Figure 3b is a functional schematic diagram of the wake-up module of the analyte detection device including a photosensitive element according to an embodiment of the present invention
  • Figure 4a is a schematic structural diagram of an analyte detection system including magnetic components and magnetic sensing elements according to an embodiment of the present invention
  • Figure 4b is a schematic structural diagram of the wake-up module of the analyte detection device including a magnetic sensing element according to an embodiment of the present invention
  • Figure 4c is a functional schematic diagram of the wake-up module of the analyte detection device including a magnetic sensing element according to an embodiment of the present invention
  • Figure 5a is a schematic structural diagram of an analyte detection system including an acceleration sensor according to an embodiment of the present invention
  • Figure 5b is a schematic structural diagram of the wake-up module of the analyte detection device including an acceleration sensor according to an embodiment of the present invention
  • Figure 5c is a functional schematic diagram of the wake-up module of the analyte detection device including an acceleration sensor according to an embodiment of the present invention
  • Figure 6 is a schematic diagram of the communication connection between the analyte detection device and external equipment according to an embodiment of the present invention
  • Figure 7 is a schematic flow chart of establishing a communication connection between an analyte detection device and an external device according to an embodiment of the present invention
  • Figures 8a-8c are schematic diagrams of the layout of the antenna of the analyte detection device according to the embodiment of the present invention.
  • FIG. 9 is a schematic circuit diagram of the wake-up module of the analyte detection device according to the embodiment of the present invention.
  • analyte detection devices emit signals to the outside world after leaving the factory. When users use them, they let the handheld device search for these broadcast signals to complete pairing and establish a communication connection. In this way, the method of transmitting signals immediately after leaving the factory will pass.
  • the battery consumes a lot of energy, making it difficult to meet the long-term use requirements of the analyte detection device.
  • the present invention provides an energy-saving analyte detection system.
  • the processor Before the analyte detection device is installed, the processor is powered on but in a deep sleep state, and the transmitter does not transmit signals outward. After the analyte detection device is installed, , triggered by predetermined conditions, the processor switches to the working state and sends The transmitter starts to emit signals to the outside world, which can save battery energy consumption and extend the service life of the analyte detection device.
  • FIG. 1 is a schematic structural diagram of an analyte detection system according to an embodiment of the present invention.
  • the analyte detection system 10 includes an auxiliary installer 101 and an analyte detection device 102.
  • the auxiliary installer 101 includes a housing 1011 and an auxiliary installation module 1012.
  • the auxiliary installation module 1012 is an ejection mechanism located inside the housing 1011.
  • the analyte detection device 102 is located at the ejection end of the auxiliary installation module 1012.
  • the auxiliary installation module 1012 can quickly install the analyte detection device 102 to the user's skin surface during use.
  • FIG. 2 is a schematic structural diagram of an analyte detection device according to an embodiment of the present invention.
  • the analyte detection device 102 includes a housing 1021, a sensor 1022, a transmitter 1023, an internal circuit 1024, a battery 1025 and a wake-up module 1026.
  • the sensor 1022 includes an external part 10221 and an internal part 10222.
  • the external part 10221, the transmitter 1023, the internal circuit 1024, the battery 1025 and the wake-up module 1026 are all located inside the housing 1021.
  • the internal part 10222 passes through the through hole 10211 on the housing 1021 to the outside of the housing. , so that it can be easily penetrated into the user's skin to detect analyte parameter information.
  • the through hole 10211 is located on the side of the housing 1021 away from the housing 1011, and at the same time, a tape (not shown in the figure) is also provided on this side. , the adhesive tape is used to adhere and fix the analyte detection device 102 on the surface of the user's skin.
  • the extracorporeal part 10221 is electrically connected to the transmitter 1023 through the internal circuit 1024 and can transmit analyte parameter information to external devices.
  • the housing 1021 of the analyte detection device 102 and the housing of the auxiliary installer 101 1011 releasable connection here "releasable connection” means that the shell 1021 and the shell 1011 are connected together through buckles, clamps, etc., and under the action of the ejection mechanism of the auxiliary installation module 1012, the shell 1021 can be connected to the shell 1011 separation.
  • the auxiliary installer 101 can provide a stable internal environment for the analyte detection device 102 .
  • the user removes the entire analyte detection device from the user's skin surface, discards it all and replaces it with a new analyte detection device. It is conducive to maintaining the best use condition of each component and improving the reliability of the analyte detection device.
  • the analyte detection device 102 When the analyte detection device 102 is installed on the user's skin surface and starts to be used, it needs to establish communication with external devices such as PDM (Personal Diabetes Manager), mobile phones, etc., and conduct data interaction to transmit the detected analyte information in the user's body to External equipment.
  • PDM Personal Diabetes Manager
  • mobile phones etc.
  • the analyte detection device 102 Before the analyte detection device 102 formally establishes communication with the external device, it is in a dormant state and transmits signals to the external device at the first frequency.
  • the analyte detection device 102 transmits signals to external devices at a lower first frequency in the sleep state to reduce battery energy consumption.
  • the first frequency is 0 to 12 times/hour. In a more preferred embodiment of the present invention, the first frequency is 0 times/hour, that is, the analyte detection device 102 does not transmit signals to external devices in the sleep state.
  • the wake-up module 1026 wakes up the analyte detection device 102 according to the trigger condition, makes it enter the working state, and transmits a signal to the external device at the second frequency, and waits for the external device to respond. Then communication is established.
  • the second frequency is higher than the first frequency. In a preferred embodiment of the present invention, the second frequency is 12 to 3600 times/hour. In a more preferred embodiment of the present invention, the second frequency is 30 times/hour.
  • Figure 3a is a schematic structural diagram of a wake-up module of an analyte detection device including a photosensitive element according to an embodiment of the present invention.
  • Figure 3b is a functional schematic diagram of the wake-up module of the analyte detection device including the photosensitive element according to the embodiment of the present invention.
  • the wake-up module 1026 includes a photosensitive element 10261, such as a photoelectric switch.
  • a photosensitive element 10261 such as a photoelectric switch.
  • the photosensitive element 10261 When there is no light beam or a weak light beam, the photosensitive element 10261 is in an open circuit state. When there is a light beam, the photosensitive element 10261 is in a closed circuit state.
  • the transmitter 1023 is connected to the battery 1025 through the internal circuit 1024, forming To form a closed loop, a wake-up module 1026 is connected to the line, and a photosensitive element 10261 is connected to the wake-up module 1026.
  • the trigger condition of the wake-up module 1026 is the change in light intensity received by the photosensitive element 10261.
  • the trigger condition of the wake-up module 1026 is that the light intensity received by the photosensitive element 10261 changes from weak to strong.
  • the analyte detection device 102 is not installed in front of the user's skin surface, the analyte detection device 102 is not separated from the auxiliary installer 101, and the shell 1021 and the shell 1011 form a sealed and light-proof space, and the auxiliary installation is
  • the detector 101 can provide a stable light-shielding environment for the analyte detection device 102. Since the light-transmitting area 10211 of the housing 1021 is located at one end close to the housing 1011, there is no external light beam irradiating the photosensitive element 10261 at this time.
  • the battery 1025 passes through the wake-up module 1026 (including the photosensitive element 10261) supplies power to the emitter 1023, the photosensitive element 10261 is in an open circuit state, the emitter 1023 is in a dormant state, and the analyte detection device 102 emits a signal to an external device at the first frequency.
  • the housing 1021 is separated from the housing 1011, and external light shines on the photosensitive element 10261 through the housing 1021.
  • the photosensitive element 10261 is in a closed circuit state, and the emitter 1023 enters the working state.
  • the analyte detection device 102 transmits a signal to the external device at the second frequency, establishes communication after the external device responds, and transmits analyte detection data to the external device.
  • the shell 1021 is made of a light-transmitting material, such as polymethylmethacrylate (PMMA), polystyrene (PS), polycarbonate (PC) or poly-4-methyl-1-pentene ( TPX), the light transmittance of the above-mentioned material is 40% to 95%.
  • PMMA polymethylmethacrylate
  • PS polystyrene
  • PC polycarbonate
  • TPX poly-4-methyl-1-pentene
  • the housing 1021 includes a light-transmitting area 10211, and the light transmittance of the light-transmitting area 10211 is higher than that of the housing 1021, so that more external light beams can illuminate the photosensitive element 10261 and increase the sensitivity of the photosensitive element 10261.
  • the light intensity changes to improve the reliability of the photosensitive element 10261.
  • the light-transmitting area 10211 includes at least one light-transmitting hole, or an array combination of multiple light-transmitting holes.
  • the light-transmitting hole can allow more external light beams to illuminate the photosensitive element 10261, further increasing the change in illumination intensity of the photosensitive element 10261, and improving the reliability of the photosensitive element 10261.
  • a light-transmitting film (not shown in the figure) is provided in the light-transmitting hole, which can prevent external water droplets, dust and other dirt from entering the interior of the analyte detection device through the light-transmitting hole, thereby improving the reliability of the device. sex.
  • the photosensitive element 10261 can sense visible light or invisible light, such as infrared rays or ultraviolet rays. In the preferred embodiment of the present invention, the photosensitive element 10261 can sense See light so that users can wake up the analyte detection device indoors or outdoors.
  • the open-circuit and closed-circuit switching conditions of the photosensitive element are to switch from weak beam irradiation to strong beam irradiation, that is, before the shell 1021 is separated from the shell 1011, a weak external beam is allowed to illuminate the inside of the shell 1011.
  • the photosensitive element 10261 receives weak light, but is still in an open circuit state, and the emitter 1023 is in a dormant state. This is because the actual connection between the housing 1021 and the housing 1011 is not completely sealed. After the shell 1021 is separated from the shell 1011, external light shines on the photosensitive element 10261 through the shell 1021 or the light-transmitting area 10211.
  • the intensity of the light received by the photosensitive element 10261 becomes stronger. After reaching the set light intensity threshold, the photosensitive element 10261 switches. In the closed-circuit state, the transmitter 1023 enters the working state, transmits a signal to the external device at the second frequency, establishes communication after the external device responds, and transmits analyte detection data to the external device.
  • Figure 4a is a schematic structural diagram of an analyte detection system including a magnetic component and a magnetic sensing element according to an embodiment of the present invention.
  • Figure 4b is a schematic structural diagram of the wake-up module of the analyte detection device including a magnetic sensing element according to an embodiment of the present invention.
  • Figure 4c is a functional schematic diagram of the wake-up module of the analyte detection device including the magnetic sensing element according to the embodiment of the present invention.
  • the magnetic component 203 is provided on the housing 2011, and the magnetic sensing element 20261 is provided in the wake-up module 2026.
  • the magnetic component 203 provides a stable magnetic field.
  • the magnetic induction element 20261 is located within the magnetic field of the magnetic component 203 and induces the magnetic field of the magnetic component 203 to generate a signal.
  • the triggering condition of the wake-up module 2026 is the change in the magnetic field sensed by the magnetic sensing element 20261.
  • the transmitter 2023 is connected to the battery 2025 through an internal circuit 2024 to form a closed loop.
  • a wake-up module 2026 is connected to the line.
  • the battery 2025 supplies power to the transmitter 2023 through the wake-up module 2026 (including the magnetic induction element 20261).
  • the analyte detection device 202 is not separated from the auxiliary installer 201, and the relative position is fixed.
  • the magnetic field sensed by the magnetic element 20261 of the magnetic component 203 is stable.
  • the magnetic induction element 20261 Under the stable magnetic field , the magnetic induction element 20261 is in an open circuit state, the transmitter 2023 is in a dormant state, and the analyte detection device 202 transmits a signal to the external device at the first frequency.
  • the analyte detection device 202 After the analyte detection device 202 is installed on the user's skin surface through the auxiliary installation module 2012, the outer shell 2021 is separated from the housing 2011, and the distance between the magnetic induction element 20261 and the magnetic part 203 changes, so the induced magnetic field also changes, and the magnetic induction
  • the element 20261 switches to a closed circuit state, the transmitter 2023 enters the working state, the analyte detection device 202 transmits a signal to the external device at the second frequency, establishes communication after the external device responds, and transmits the analyte detection data to the external device.
  • the magnetic sensing element 20261 senses the magnetic field intensity or magnetic field direction of the magnetic component 203 .
  • the magnetic sensing element 20261 includes a Hall element (not shown in the figure), which can sensitively sense changes in the magnetic field intensity of the magnetic component 203 .
  • the magnetic component 203 may be an individual part independent of the housing 2011 , or may be a part of the housing 2011 and embedded in the housing 2011 .
  • the housing 2011 is embedded or encased with a magnetic field shielding device (not shown in the figure), such as a Faraday cage.
  • a magnetic field shielding device such as a Faraday cage.
  • the magnetic field shielding device is located outside the magnetic component 203 to reduce the impact of the external magnetic field on the magnetic sensing element 20261.
  • Figure 5a is a schematic structural diagram of the wake-up module of the analyte detection system including an acceleration sensor according to an embodiment of the present invention.
  • Figure 5b is a schematic structural diagram of the wake-up module of the analyte detection device including an acceleration sensor according to an embodiment of the present invention.
  • Figure 5c is a functional schematic diagram of the wake-up module of the analyte detection device including an acceleration sensor according to the embodiment of the present invention.
  • the wake-up module 3026 includes an acceleration sensor 30261.
  • the acceleration sensor 30261 can sensitively sense motion parameter values such as acceleration, and adjust the circuit status of the wake-up module 3026 accordingly.
  • the trigger condition of the wake-up module 3026 is the change of the motion parameter of the acceleration sensor 30261.
  • the transmitter 3023 is connected to the battery 3025 through an internal circuit 3024 to form a closed loop.
  • a wake-up module 3026 is connected to the line.
  • the battery 3025 supplies power to the transmitter 3023 through the wake-up module 3026 (including the acceleration sensor 30261).
  • the auxiliary installation module 3012 uses an ejection mechanism 30121, such as a spring and other elastic parts, and the auxiliary needle 30122 can quickly pierce the body part 30222 into the user's skin.
  • the ejection mechanism 30121 generates an instantaneous large forward acceleration a1 when used. After being installed on the user's skin surface, it is blocked by the skin and generates a reverse acceleration a2. After the acceleration sensor 30261 senses the above two accelerations, it can determine the detection of the analyte.
  • Device 302 is mounted to the surface of the user's skin.
  • the analyte detection device 302 is installed in front of the user's skin surface, the wake-up module 3026 is in an open circuit state, the transmitter 3023 is in a sleep state, and the analyte detection device 302 transmits signals to external devices at a first frequency.
  • the acceleration sensor 30261 determines that the analyte detection device 302 is installed on the user's skin surface
  • the wake-up module 3026 switches to a closed-circuit state, and the transmitter 3023 enters the working state
  • the analyte detection device 302 transmits a signal to the external device at the second frequency, establishes communication after the external device responds, and transmits the analyte detection data to the external device.
  • first frequency and second frequency in this patent both refer to the transmission frequency of the signal to represent the length of the transmission interval of the signal.
  • Figure 6 is a schematic diagram of the communication connection between the analyte detection device and external equipment according to the embodiment of the present invention.
  • the analyte detection device 102 is activated immediately after entering the working state, emits a first signal before establishing communication with the external device 103, and emits a second signal after establishing communication with the external device 103.
  • the difference between the first signal and the second signal lies in signal frequency, signal type, signal strength or/and signal format.
  • the first signal uses Bluetooth Low Energy (BLE), and the second signal uses Near Field Communication (NFC); or the first signal uses WiFi, and the second signal uses Bluetooth Low Energy (BLE). ).
  • BLE Bluetooth Low Energy
  • NFC Near Field Communication
  • WiFi Wireless Fidelity
  • BLE Bluetooth Low Energy
  • the first signal and the second signal are signals of the same type, but their signal strengths are different.
  • the signal strength of the first signal is weaker than the signal strength of the second signal.
  • the effective range of the first signal is 0-10m
  • the effective range of the second signal is 0-10m.
  • the effective range of the first signal is 0 to 1 m. A smaller effective range of the first signal facilitates the external device 103 to filter out erroneous first signals.
  • the first signal and the second signal have different signal formats.
  • the communication connection status of the first signal data packet is marked A
  • the communication connection status of the second signal data packet is marked B.
  • the above-mentioned mark can be located in any position of the data packet, such as the header of the data packet, or the packet body, etc.
  • the header of the data packet is set as the communication connection status flag bit.
  • multiple mark positions of the data packet are set as communication connection status marks.
  • the first signal data packet sent by the analyte detection device is A...A...A ...
  • the second signal data packet sent by the analyte detection device is B...B...B....
  • the form of the communication connection status mark A(B) in the data packet may be a single byte, such as 0(1), or may be multiple bytes, such as 000(111), which is not limited here.
  • the first signal and the second signal have different signal frequencies.
  • the first signal is a low-frequency signal and the second signal is a high-frequency signal
  • the first signal is a high-frequency signal and the second signal is a high-frequency signal.
  • the second signal is a low-frequency signal.
  • the difference between the first signal and the second signal lies in both signal format and signal strength, or both in signal format, signal strength, signal frequency, or other signal distinction forms. combination.
  • the combination of multiple differentiated forms of signals is more conducive to external equipment distinguishing the analyte detection device to be connected.
  • the first signal can be distinguished from the second signal, technical solutions including but not limited to the above can be used, which are not limited here. Regardless of how the first signal and the second signal are distinguished, the characteristics of the first signal and the second signal are pre-stored in the external device 103 .
  • Figure 7 is a schematic flowchart of establishing a communication connection between the analyte detection device and external equipment according to the embodiment of the present invention.
  • the user when the user needs to establish a communication connection between the analyte detection device 102 and the external device 103 , he first places the external device 103 near the analyte detection device 102 and confirms that there are as few devices around as possible. Other analyte detection devices. After the user starts the external device 103, the external device 103 searches for and identifies nearby signals.
  • the external device 103 If the external device 103 only recognizes a first signal, it can be determined that the signal is a signal emitted by the analyte detection device 102 to be established for communication connection, and Establishing a communication connection with the analyte detection device 102 through the signal link eliminates the need for the user to manually input or scan the device code of the analyte detection device 102, simplifying the process of establishing a communication connection, avoiding the user from inputting or scanning the wrong device code, and improving user experience.
  • the external device 103 prompts the user to confirm whether to connect, so as to improve the reliability of the communication connection between the analyte detection device 102 and the external device 103.
  • the external device 103 if the user is in a complex environment, that is, the external device 103 recognizes multiple first signals, or multiple first signals and second signals, the external device 103 cannot determine the analyte detection to be established to establish a communication connection.
  • the first signal emitted by the device 102 in this case, the external device 103 prompts the user to manually input or scan the device code of the analyte detection device 102 to be established to establish a communication connection, in order to establish a communication connection with the analyte detection device 102.
  • the external device 103 when the user is in a complex environment and the external device 103 is unable to determine the first signal transmitted by the analyte detection device 102 to establish a communication connection, the external device 103 prompts the user to change the operating location, and the user needs to carry the communication connection to be established.
  • the communication-connected analyte detection device 102 and the external device 103 go to other locations, until the external device 103 only recognizes a first signal, it can be determined that the signal is a signal transmitted by the analyte detection device 102 to be established, and the communication connection is Pass Establishing a communication connection with the analyte detection device 102 through the signal link eliminates the need for the user to manually input or scan the device code of the analyte detection device 102, simplifying the process of establishing a communication connection, avoiding the user from inputting or scanning the wrong device code, and improving user experience.
  • the external device 103 if the external device 103 does not recognize the first signal within the effective range, it is determined that the analyte detection device 102 is not working normally. At this time, the external device 103 issues an alarm or fault prompt to the user to remind the user. Check or replace the analyte detection device.
  • the prompt from the external device 103 may be in one or more forms such as audio, video, or vibration.
  • the prompt of the external device 103 when the prompt of the external device 103 is audio, the external device 103 emits "beep" prompt sounds of different lengths and/or different time intervals according to different prompt needs.
  • the prompt of the external device 103 when the prompt of the external device 103 is a video, different text prompts are displayed on the display screen according to different prompt needs.
  • the prompt of the external device 103 is vibration, the external device 103 vibrates with different lengths and/or different time intervals according to different prompt needs.
  • the transmitter 1023 includes communication elements such as an antenna 10231.
  • the antenna 10231 is composed of a conductive coil. According to the requirements for the analyte detection device 302 to communicate with external devices, the conductive coil of the antenna 10231 needs to be accurately designed and layout to tailor specific characteristics such as inductance, resonance, and losses.
  • the conductive coil of the antenna is soft, it needs to be attached to a non-deformable substrate to prevent its inductance and other characteristics from changing during use.
  • the substrate material the antenna is attached to it can be divided into ceramic antenna, PCB antenna and FPC antenna.
  • Ceramic antennas use a combination of high and low temperature firing to print conductive coils on ceramic substrates.
  • the formed ceramic antennas take up little space and have good performance, but have narrow bandwidth and are difficult to achieve multi-band;
  • PCB antennas are based on PCB
  • the antenna is based on a PCB board, and a conductive coil of a specific length is fixed on the PCB board.
  • the molded PCB antenna is low-cost and does not require separate antenna assembly and repeated debugging.
  • the PCB antenna is only suitable for a single frequency band and may vary between different batches. There is a certain deviation, and it is easily interfered by the current on the PCB board; the FPC antenna is based on FPC (Flexible Printed Circuit, flexible circuit board).
  • the FPC antenna has high space utilization, low cost, good performance, and is suitable for small Intelligent electronic devices are used, but each FPC antenna needs to be individually debugged before use, and the installation is inconvenient.
  • the base material on which the conductive coil is attached is plastic, tape, etc.
  • conductive coils of specific lengths are printed inside
  • the circuit board of the circuit 1024 serves as an antenna (not shown in the figure) of the transmitter 1023 to implement the functions of transmitting signals to external devices and receiving signals. If the antenna on the internal circuit 1024 is transferred and printed on other components of the analyte detection device 102, the circuit board volume of the internal circuit 1024 can be reduced, thereby achieving a miniaturized design of the analyte detection device 102.
  • the antenna 10231 is arranged outside the casing of the battery 1025.
  • the circuit board of the internal circuit 1024 no longer needs to carry the antenna 10231.
  • the volume of the circuit board occupied by the antenna 10231 can be reduced, thereby enabling analysis Miniaturized design of the object detection device 102.
  • the conductive coil of the antenna 10231 is fixed on the outer shell surface of the battery 1025 using technologies such as LDS (Laser Direct Structuring), printing or case inlay, and the antenna 10231 is then connected through a wire ( (not shown in the figure) is connected to the control circuit of the transmitter 1023.
  • the transmitting and receiving signal frequencies of the antenna 10231 are highly sensitive to the inductance of the conductive coil, and the battery 1025 contains metal and other highly conductive materials inside, which may cause eddy currents during the operation of the antenna 10231, and these eddy currents may Reduce the inductance of the conductive coil, thereby affecting the working performance of the antenna 10231. Therefore, the conductive coil arranged on the surface of the battery 1025 shell also needs to take measures to reduce eddy current. For example, replacing the metal shell of the battery 1025 with PC, ceramic, PP, etc. can reduce the eddy current. Materials affected by small eddies.
  • the antenna 10231 is not limited to being arranged on the upper end surface of the battery 1025 shown in Figure 6a, but can also be arranged on the side or lower end surface of the battery 1025, or part of it is arranged on the upper end surface, and the other part is arranged on the side or From the bottom section, those skilled in the art can understand that the antenna 10231 is arranged outside the case of the battery 1025, and may include all surfaces outside the case of the battery 1025.
  • the antenna 10231 can also be provided on the housing 1021 of the analyte detection device 102.
  • technologies such as LDS, printing or shell inlay are used to fix the conductive coil of the antenna 10231 on the surface of the housing 1021.
  • the conductive coil of the antenna 10231 is fixed on the inner surface of the housing 1021. It can prevent external dirt from contaminating the antenna 10231.
  • the antenna 10231 may be located in the upper housing 10211 or the lower housing 10212, or part of the antenna 10231 may be located in the upper housing 10211 and the other part may be located in the lower housing 10212 to fully utilize the internal space of the analyte detection device 102.
  • the two parts of the conductive coil are connected through wires to form a three-dimensional antenna, which can further improve the utilization of the internal space of the housing. Rate.
  • the antenna 10231 can also be disposed on the adhesive tape 104.
  • LDS, printing or lamination technology is used to fix the conductive coil of the antenna 10231 on the surface or interlayer of the adhesive tape 104.
  • the antenna 10231 is fixed in the interlayer of the tape 104 to prevent contamination from external stolen goods.
  • the adhesive tape 104 may be required to have some appropriate hardness to prevent the adhesive tape 104 from bending or bending due to the user's muscle peristalsis, which will affect the performance of the antenna 10231 arranged thereon. performance and may even destroy the antenna 10231.
  • the conductive coil of the antenna 10231 can be arranged on the base material in a curled manner as shown in Figures 6a-6c, or can be bent at a fixed angle, at an irregular angle, or in other irregular ways.
  • the arrangement of its conductive coils on the base material is not specifically limited.
  • the conductive coil of the antenna 10231 can be arranged on different substrates, for example, part of it is arranged on the outside of the casing of the battery 1025, and part of it is arranged on the inner surface of the housing 1021 of the analyte detection device 102, Or a part of it is arranged in the adhesive tape 104.
  • the antenna 10231 can realize its function of transmitting and receiving communication signals at a predetermined frequency, the arrangement position of its conductive coil on the base material is not specifically limited.
  • the antenna 10231 can be composed of multiple conductive coils of the same or different lengths, and are electrically connected to the control circuit of the transmitter 1023 respectively to form multiple antennas, which can be used to transmit and receive communication signals of different frequencies. .
  • multiple antennas can transmit or receive communication signals at the same time or at different times through instructions from the control circuit of the transmitter 1023.
  • one of the plurality of antennas may be set as a main antenna, and the other antennas may be set as secondary antennas.
  • the control circuit of the transmitter 1023 controls the main antenna to transmit a signal to the outside world at the first frequency. After the analyte detection device 102 is converted to the working state, the control circuit controls the main antenna to transmit a signal to the outside world at the first frequency. The circuit controls the main antenna to transmit signals to the outside world at the second frequency.
  • the control circuit of the transmitter 1023 controls the main antenna to transmit a signal to the outside world at the first frequency. After the analyte detection device 102 is converted to the working state, the control circuit controls the main antenna to transmit a signal to the outside world at the first frequency. The circuit controls the secondary antenna to transmit signals to the outside world at the second frequency.
  • the control circuit of the transmitter 1023 controls the secondary antenna to transmit a signal to the outside world at the first frequency. After setting 102 to the working state, the control circuit controls the main antenna to transmit signals to the outside world at the second frequency.
  • the control circuit of the transmitter 1023 controls the main antenna to transmit a signal to the outside world with the first signal strength. After the analyte detection device 102 is converted to the working state, The control circuit controls the main antenna to transmit signals to the outside world with a second signal strength.
  • the control circuit of the transmitter 1023 controls the main antenna to transmit a signal to the outside world with the first signal strength. After the analyte detection device 102 is converted to the working state, The control circuit controls the secondary antenna to transmit signals to the outside world with a second signal strength.
  • the control circuit of the transmitter 1023 controls the secondary antenna to transmit a signal to the outside world with the first signal strength.
  • the control circuit controls the main antenna to transmit signals to the outside world with a second signal strength.
  • the first signal strength is weaker than the second signal strength.
  • multiple antennas may be arranged on the same non-circuit board substrate, or may be arranged on different non-circuit board substrates.
  • multiple antennas can be arranged on the non-circuit board substrate in a curled manner, or can be bent at a fixed angle, bent at an irregular angle, or arranged in other irregular ways on the non-circuit board substrate. superior.
  • Circuit embodiment for realizing the function of wake-up module 1026.
  • the analyte detection device 102 before the analyte detection device 102 is installed on the user's skin surface, in order to extend the service life of the battery 1025 as much as possible and reduce the energy consumption of the battery 1025, the analyte detection device 102 is in a dormant state; analyte detection After the device 102 is installed on the user's skin surface through the auxiliary installation module 1012, it is awakened and enters the working state.
  • Figure 9 is a circuit embodiment of the function of the wake-up module 1026 that implements the above functions.
  • the electronic components of the wake-up module 1026 circuit include a photosensitive element 10261, a processor 10262, a PMOS tube (field effect transistor) 10263, a first resistor R1 and a second resistor R2.
  • Each electronic component implements logic according to the circuit. Operably connected and powered by battery 1025. Specifically, the a terminal of the photosensitive element 10261 is connected to the battery 1025 through the resistor R1, the c and d interfaces of the processor 10262 are respectively connected to both ends of the resistor R1, the source of the PMOS tube 10263 is connected to the battery 1025, and the gate is connected to the processor.
  • the e-interface of 10262 is connected, and the drain is connected to the working module.
  • the working module here refers to the general name of the necessary working components of the analyte detection device 102 including at least the antenna 10231.
  • the second resistor R2 The b end of the photosensitive element 10261, the g interface of the processor and the working module are all grounded.
  • the first resistor R1 is a pull-up resistor.
  • the d terminal of the processor 10262 is at a high level;
  • the second resistor R2 is a pull-up resistor.
  • the gate of PMOS e terminal
  • the above electronic components are necessary components for the wake-up module 1026 circuit.
  • auxiliary components such as voltage stabilizing components can also be added, which will not be described in detail here.
  • the working module may also include electronic components such as a sensor detection circuit, a buzzer, and an LED light.
  • the photosensitive element 10261 can be specifically a photodiode, a photoelectric sensor, a photoresistor, etc.
  • the photosensitive element 10261 is a photodiode.
  • the photodiode has good insulation properties when not exposed to light, and has good conductive properties when exposed to light.
  • the analyte detection device 102 before use, the analyte detection device 102 is fixed in the auxiliary installer 101.
  • the auxiliary installer 101 provides a stable environment for the analyte detection device 102, such as a stable light-shielding environment through which external light beams cannot pass.
  • the auxiliary installer 101 irradiates the analyte detection device 102 to prevent the photosensitive element 10261 from being triggered.
  • the analyte detection device 102 is separated from the auxiliary installer 101.
  • the auxiliary installer 101 no longer provides a light-shielding environment for the analyte detection device.
  • the external light beam can illuminate the analyte detection device 102 and then illuminate the photosensitive element. 10261, the photosensitive element 10261 is triggered.
  • the photosensitive element 10261 is in an open circuit state when not illuminated by a light beam, and both the c interface and the d interface of the processor 10262 are at a high level.
  • the resistance of the first resistor R1 can be set, for example, 10 M ⁇ . , causing a weak current to pass through the processor 10262, that is, the processor 10262 is powered on after the analyte detection device 102 leaves the factory, and is in a deep sleep state.
  • the gate of the PMOS tube 10263 is connected to the battery 1025 through the second resistor R2 and is in a high level state.
  • the PMOS tube 10263 is in an open circuit and the battery 1025 cannot supply power to the working module.
  • the circuit of the wake-up module 1026 may not include the second resistor R2.
  • the interface e When the processor 10262 is in the deep sleep state, the interface e provides a high level to the gate of the PMOS tube 10263, so that the PMOS tube 10263 In the open circuit state, after the processor 10262 switches to the working state, the interface e provides a low level to the gate of the PMOS tube 10263, so that the PMOS tube 10263 is in a closed circuit state.
  • the battery 1025 only provides a weak current to the processor 10262. In this way, the electronic components do not need to be used before the analyte detection device 102 is officially used. It will consume too much power of the battery 1025 and extend the service life of the battery 1025.
  • the analyte detection device 102 is separated from the auxiliary installer 101, and the photosensitive element 10261 is irradiated by the light beam and is in a closed circuit state.
  • the level of the d interface of the processor 10262 decreases, and the processor 10262 switches to the working state.
  • the level of the e interface of the processor 10262 decreases, and the gate of the PMOS tube 10263 decreases to a low level.
  • the PMOS tube 10263 changes to a closed-circuit state, the working module can obtain power from the battery 1025 and enter the working state, and the transmitter 1023 starts to transmit signals to the outside world.
  • the processor 10262 once the processor 10262 is converted to the working state, its e interface is continuously controlled to a low level, which allows the PMOS tube 10263 to continue to be turned on, regardless of whether the photosensitive element 10261 can still receive light beam irradiation in the future.
  • the battery 1025 can continue to provide power for the working module, that is, after the processor 10262 switches to the working state, the state of the photosensitive element 10261 will not affect the circuit state of the wake-up module 1026.
  • entering the working state from the dormant state means that the electronic components in the working module are changed from unpowered to powered on.
  • the antenna 10231 transmits a signal to the outside world with the first signal strength, and the analyte detection device 102 establishes a communication connection with the external device. Then, the antenna 10231 transmits a signal to the outside world with the second signal strength, and the first signal strength is weaker than the second signal strength.
  • the sensor detection circuit starts to work, and the sensor 1022 is connected to the working current, which can detect analyte parameter information in the user's body.
  • the antenna 10231 transmits a signal to the outside world at the first frequency.
  • the antenna 10231 transmits signals to the outside world at the second frequency, and the first frequency is lower than the second frequency.
  • the photosensitive element 10261 in the wake-up module 1026 can be replaced by other state switching components, such as magnetic sensing components, touch switches, acceleration sensors, etc. These state switching components are in an open circuit state after leaving the factory, so that The processor 10262 is in a deep sleep state. After the conditions are triggered, these state switching components are changed to a closed-circuit state, and the processor 10262 is changed to a working state. status, the working module starts working, and the relevant circuit implementation process will not be described here.
  • state switching components such as magnetic sensing components, touch switches, acceleration sensors, etc.
  • embodiments of the present invention disclose an energy-saving analyte detection system.
  • the processor Before the analyte detection device is installed, the processor is powered on but in a deep sleep state, and the transmitter does not transmit signals outward. After installation, after predetermined conditions are triggered, the processor switches to the working state, and the transmitter begins to transmit signals to the outside world, which can save battery energy consumption and extend the service life of the analyte detection device.

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Abstract

一种节能分析物检测系统（10），包括：分析物检测装置（102），以及用于将分析物检测装置（102）安装在用户皮肤表面的辅助安装器（101）；分析物检测装置（102）至少包括发射器（1023）和传感器（1022），其中发射器（1023）包括电池（1025）、唤醒模块（1026）和工作模块（10231），唤醒模块（1026）包括处理器（10262）、状态切换构件（10261）和场效应晶体管（10263）。安装前，状态切换构件（10261）开路，处理器（10262）上电但处于深度休眠状态，并使场效应晶体管（10263）开路，发射器（1023）不向外发射信号，在分析物检测装置（102）安装后，状态切换构件（10261）闭路，处理器（10262）转换为工作状态，发射器（1023）开始向外界发射信号，该系统能够节省电池的能量消耗，延长分析物检测装置的使用寿命。

Description

节能分析物检测系统
相关申请的交叉引用
本申请要求以下专利申请的权益并要求其优先权：2022年5月12日提交的中国专利申请，申请号为CN202210516562.6；2022年6月17日提交的PCT专利申请，申请号为PCT/CN2022/099387；2022年8月1日提交的PCT专利申请，申请号为PCT/CN2022/109439。
技术领域
本发明主要涉及医疗器械领域，特别涉及一种节能分析物检测系统。
背景技术
正常人身体中的胰腺可自动检测人体血液中的葡萄糖含量，并自动分泌所需的胰岛素/胰高血糖素。而糖尿病患者胰腺的功能出现异常状况，无法正常分泌人体所需胰岛素。因此糖尿病是人体胰腺功能出现异常而导致的代谢类疾病，糖尿病为终身疾病。目前医疗技术尚无法根治糖尿病，只能通过稳定血糖来控制糖尿病及其并发症的发生和发展。
糖尿病患者在向体内注射胰岛素之前需要检测血糖。目前多数的检测手段可以对血糖连续检测，并将血糖数据实时发送至外界设备，便于用户查看，这种检测方法称为连续葡萄糖检测(Continuous Glucose Monitoring，CGM)。
分析物检测装置由于小型化设计的需求，其内放置的电池不会太大，因而电池容量也不会太大，在使用分析物检测装置时需要考虑电池的续航能力，现有分析物检测装置在出厂后便向外界发射信号，用户在使用时让手持设备搜索这些广播信号以完成配对，并建立通信连接，这样出场后即发射信号的方式会过多地消耗电池的能量，难以满足分析物检测装置长时间使用地需求。
因此，现有技术亟需一种更加节能的分析物检测系统。
发明内容
本发明公开了一种节能分析物检测系统，在分析物检测装置安装前，处理器上电但处于深度休眠状态，发射器不向外发射信号，在分析物检测装置安装后，经过预定条件触发，处理器转换为工作状态，发射器开始向外界发 射信号，能够节省电池的能量消耗，延长分析物检测装置的使用寿命。
本发明实施例公开了一种分析物检测装置，包括：辅助安装器，用于将分析物检测装置安装在用户皮肤表面；分析物检测装置，至少包括发射器和传感器，发射器至少包括电池、唤醒模块和工作模块，唤醒模块将电池和工作模块电连接；其中，唤醒模块至少包括处理器、状态切换构件和场效应晶体管；其中，状态切换构件在触发前为开路，处理器上电并处于深度休眠状态，并使场效应晶体管开路，电池不向工作模块提供电能；在状态切换构件触发后为闭路，处理器转换为工作状态，并使场效应晶体管闭路，电池向所述工作模块提供电能；其中，在处理器转换为工作状态后，使场效应晶体管锁定为闭路，以使电池持续为工作模块提供电能。
根据本发明的一个方面，状态切换构件为感光元件、磁感元件、触控开关或加速度传感器中的一种；
根据本发明的一个方面，状态切换构件为光电二极管。
根据本发明的一个方面，辅助安装器还用于为分析物检测装置提供稳定环境，在使用前，防止状态切换构件被触发。
根据本发明的一个方面，辅助安装器为分析物检测装置提供光屏蔽环境。
根据本发明的一个方面，在分析物检测装置与辅助安装器分离后，辅助安装器不再为分析物检测装置提供光屏蔽环境，状态切换构件被触发。
根据本发明的一个方面，工作模块至少包括天线。
根据本发明的一个方面，在工作模块被提供电能后，天线以第一频率或第一信号强度向外界发射信号。
根据本发明的一个方面，传感器为葡萄糖传感器。
与现有技术相比，本发明的技术方案具备以下优点：
本发明公开的分析物检测系统，在使用辅助安装器前，分析物检测装置中唤醒模块的处理器处于上电但深度休眠状态，发射器不向外发射信号，在使用辅助安装器后，唤醒模块中的状态切换构件被触发，处理器转换为工作状态，发射器向外发射信号，能够在分析物检测装置正式使用前节省电池能量消耗，延长分析物检测装置使用寿命。
进一步的，处理器转换为工作状态后，能够将场效应晶体管锁定为闭路状态，工作模块能够被持续提供电能，而与状态切换构件所处状态无关。
附图说明
图1为根据本发明实施例分析物检测系统的结构示意图；
图2为根据本发明实施例分析物检测装置的结构示意图；
图3a为根据本发明实施例分析物检测装置唤醒模块包括感光元件的结构示意图；
图3b为根据本发明实施例分析物检测装置唤醒模块包括感光元件的功能示意图；
图4a为根据本发明实施例分析物检测系统包括磁性件和磁感元件的结构示意图；
图4b为根据本发明实施例分析物检测装置唤醒模块包括磁感元件的结构示意图；
图4c为根据本发明实施例分析物检测装置唤醒模块包括磁感元件的功能示意图；
图5a为根据本发明实施例分析物检测系统包括加速度传感器的结构示意图；
图5b为根据本发明实施例分析物检测装置唤醒模块包括加速度传感器的结构示意图；
图5c为根据本发明实施例分析物检测装置唤醒模块包括加速度传感器的功能示意图；
图6为根据本发明实施例分析物检测装置与外界设备通信连接的示意图；
图7为根据本发明实施例分析物检测装置与外界设备建立通信连接的流程示意图；
图8a-8c为本发明实施例分析物检测装置天线的布置示意图；
图9为本发明实施例分析物检测装置的唤醒模块的电路示意图。
具体实施方式
如前所述，现有分析物检测装置在出厂后便向外界发射信号，用户在使用时让手持设备搜索这些广播信号以完成配对，并建立通信连接，这样出场后即发射信号的方式会过多地消耗电池的能量，难以满足分析物检测装置长时间使用地需求。
为了解决该问题，本发明提供了一种节能分析物检测系统，在分析物检测装置安装前，处理器上电但处于深度休眠状态，发射器不向外发射信号，在分析物检测装置安装后，经过预定条件触发，处理器转换为工作状态，发 射器开始向外界发射信号，能够节省电池的能量消耗，延长分析物检测装置的使用寿命。
现在将参照附图来详细描述本发明的各种示例性实施例。应理解，除非另外具体说明，否则在这些实施例中阐述的部件和步骤的相对布置、数字表达式和数值不应被理解为对本发明范围的限制。
此外，应当理解，为了便于描述，附图中所示出的各个部件的尺寸并不必然按照实际的比例关系绘制，例如某些单元的厚度、宽度、长度或距离可以相对于其他结构有所放大。
以下对示例性实施例的描述仅仅是说明性的，在任何意义上都不作为对本发明及其应用或使用的任何限制。这里对于相关领域普通技术人员已知的技术、方法和装置可能不作详细讨论，但在适用这些技术、方法和装置情况下，这些技术、方法和装置应当被视为本说明书的一部分。
应注意，相似的标号和字母在下面的附图中表示类似项，因此，一旦某一项在一个附图中被定义或说明，则在随后的附图说明中将不需要对其进行进一步讨论。
图1为本发明实施例分析物检测系统的结构示意图，分析物检测系统10包括辅助安装器101和分析物检测装置102，其中，辅助安装器101包括壳体1011和辅助安装模块1012，在本发明实施例中，辅助安装模块1012为弹射机构，位于壳体1011内部。分析物检测装置102位于辅助安装模块1012的弹射末端，在使用时辅助安装模块1012可将分析物检测装置102快速地安装到用户皮肤表面。
图2为本发明实施例分析物检测装置的结构示意图，分析物检测装置102包括外壳1021、传感器1022、发射器1023、内部电路1024、电池1025和唤醒模块1026。传感器1022包括体外部分10221和体内部分10222，体外部分10221、发射器1023、内部电路1024、电池1025和唤醒模块1026均位于外壳1021内部，体内部分10222穿过外壳1021上的通孔10211到外壳外部，以便于刺入用户皮下，检测分析物参数信息。本领域技术人员可以知晓的是，为了将体内部分10222刺入用户皮下，通孔10211位于外壳1021远离壳体1011的一面，同时，在该面上，还设置有胶布(图中未示出)，胶布用于将分析物检测装置102粘贴固定在用户皮肤表面。体外部分10221通过内部电路1024与发射器1023电连接，可将分析物参数信息传输到外界设备。
在使用前，分析物检测装置102的外壳1021与辅助安装器101的壳体 1011可释放连接，这里“可释放连接”是指，外壳1021与壳体1011通过卡扣、卡箍等方式连接在一起，在辅助安装模块1012弹射机构的作用下，外壳1021可与壳体1011分离。辅助安装器101可为分析物检测装置102提供稳定的内部环境。
传感器1022使用寿命终止，或者电池1025电量消耗完毕，或者其他因素导致分析物检测装置失效后，用户将整个分析物检测装置从用户皮肤表面取下，全部抛弃后更换新的分析物检测装置，有利于各个部件保持最佳使用状态，提高分析物检测装置可靠性。
在分析物检测装置102安装到用户皮肤表面、开始使用时，需要与外界设备如PDM(Personal Diabetes Manager)、手机等建立通信，进行数据交互，以将检测到的用户体内分析物信息数据传输到外界设备。
如前文所述，在分析物检测装置102正式与外界设备建立通信前，处于休眠状态，以第一频率向外界设备发射信号。在本发明实施例中，分析物检测装置102在休眠状态下以较低的第一频率向外界设备发射信号，以减少电池能量消耗。在本发明更优选实施例中，第一频率为0～12次/小时。在本发明更优选实施例中，第一频率为0次/小时，即分析物检测装置102在休眠状态下不向外界设备发射信号。
为了使休眠状态下的分析物检测装置102与外界设备建立通信，唤醒模块1026按照触发条件唤醒分析物检测装置102，使其进入工作状态，以第二频率向外界设备发射信号，待外界设备响应后建立通信。为便于用户方便、实时地获取分析物参数信息，第二频率高于第一频率。在本发明优选实施例中，第二频率为12～3600次/小时。在本发明更优选实施例中，第二频率为30次/小时。
实施例一
感光元件
图3a为本发明实施例分析物检测装置唤醒模块包括感光元件的结构示意图。图3b为本发明实施例分析物检测装置唤醒模块包括感光元件的功能示意图。
在本发明实施例中，唤醒模块1026包括感光元件10261，如光电开关，在没有光束照射或者弱光束照射时，感光元件10261处于开路状态，有光束照射时，感光元件10261处于闭路状态。
结合图1和图3b，发射器1023通过内部电路1024与电池1025连接，形 成闭合回路，线路上连接有唤醒模块1026，唤醒模块1026内连接有感光元件10261，唤醒模块1026的触发条件为感光元件10261接收到的光线强度变化。
在本发明优选实施例中，唤醒模块1026的触发条件为感光元件10261接收到的光线强度由弱变强。
在本发明实施例中，分析物检测装置102没有被安装到用户皮肤表面前，分析物检测装置102没有与辅助安装器101分离，外壳1021与壳体1011组成密闭不透光的空间，辅助安装器101可以为分析物检测装置102提供稳定的光屏蔽环境，由于外壳1021的透光区10211位于靠近壳体1011的一端，此时没有外界光束照射在感光元件10261上，电池1025通过唤醒模块1026(包括感光元件10261)向发射器1023供电，感光元件10261处于开路状态，发射器1023处于休眠状态，分析物检测装置102以第一频率向外界设备发射信号。分析物检测装置102通过辅助安装模块1012安装到用户皮肤表面后，外壳1021与壳体1011分离，外界光通过外壳1021照射到感光元件10261上，感光元件10261处于闭路状态，发射器1023进入工作状态，分析物检测装置102以第二频率向外界设备发射信号，待外界设备响应后建立通信，并向外界设备传输分析物检测数据。
在本发明实施例中，外壳1021为透光材质，如聚甲基丙烯酸甲酯(PMMA)、聚苯乙烯(PS)、聚碳酸酯(PC)或聚4-甲基-1-戊烯(TPX)中的一种，上述材料的透光率为40％～95％，外壳1021与壳体1011分离后，外界光可通过外壳1021照射在感光元件10261上。
在本发明其他实施例中，外壳1021上包括透光区10211，透光区10211的透光率高于外壳1021，以便于更多的外界光束照射在感光元件10261上，增大感光元件10261的光照强度变化，提高感光元件10261的可靠性。
在本发明另一个实施例中，透光区10211包括至少一个透光孔，或者多个透光孔的阵列组合。透光孔可以使更多的外界光束照射在感光元件10261上，进一步增大感光元件10261的光照强度变化，提高感光元件10261的可靠性。在本发明优选实施例中，透光孔中设置有透光膜(图中未示出)，可以防止外界水滴、灰尘等脏污通过透光孔进入到分析物检测装置内部，提高装置的可靠性。
在本发明实施例中，感光元件10261可以感应可见光，也可以感应不可见光，如红外线或紫外线。在本发明优选实施例中，感光元件10261感应可 见光，以便于用户在室内或者室外均可以唤醒分析物检测装置。
在本发明另一个实施例中，感光元件的开路、闭路切换条件为弱光束照射转为强光束照射，即在外壳1021与壳体1011分离前，允许有微弱外界光束照射到壳体1011内部，感光元件10261接收微弱光线，但仍处于开路状态，发射器1023处于休眠状态，这是考虑到外壳1021与壳体1011的实际连接不是完全密封的。外壳1021与壳体1011分离后，外界光通过外壳1021或者透光区10211照射在感光元件10261上，感光元件10261接收到的光线强度变强，到达设定的光强阈值后，感光元件10261切换为闭路状态，发射器1023进入工作状态，以第二频率向外界设备发射信号，待外界设备响应后建立通信，并向外界设备传输分析物检测数据。
实施例二
磁性件和磁感元件
图4a为本发明实施例分析物检测系统包括磁性件和磁感元件的结构示意图。图4b为本发明实施例分析物检测装置唤醒模块包括磁感元件的结构示意图。图4c为本发明实施例分析物检测装置唤醒模块包括磁感元件的功能示意图。
在本发明实施例中，壳体2011上设置有磁性件203，唤醒模块2026内设置有磁感元件20261。磁性件203提供稳定磁场，磁感元件20261位于磁性件203的磁场内，并感应磁性件203的磁场以产生信号。唤醒模块2026的触发条件为磁感元件20261感应到的磁场变化。
发射器2023通过内部电路2024与电池2025连接，形成闭合回路，线路上连接有唤醒模块2026，电池2025通过唤醒模块2026(包括磁感元件20261)向发射器2023供电。分析物检测装置202没有被安装到用户皮肤表面前，分析物检测装置202没有与辅助安装器201分离，相对位置固定，磁感元件20261感应到磁性件203的磁场是稳定的，在稳定磁场下，磁感元件20261处于开路状态，发射器2023处于休眠状态，分析物检测装置202以第一频率向外界设备发射信号。分析物检测装置202通过辅助安装模块2012安装到用户皮肤表面后，外壳2021与壳体2011分离，磁感元件20261与磁性件203间的距离发生变化，因此感应到的磁场也发生变化，磁感元件20261切换为闭路状态，发射器2023进入工作状态，分析物检测装置202以第二频率向外界设备发射信号，待外界设备响应后建立通信，并向外界设备传输分析物检测数据。
在本发明实施例中，磁感元件20261感应磁性件203的磁场强度或者磁场方向。优选的，磁感元件20261包括霍尔元件(图中未示出)，可以灵敏地感应磁性件203的磁场强度变化。
在本发明实施例中，磁性件203可以是独立于壳体2011的个体零件，也可以是壳体2011的一部分，内嵌在壳体2011上。
在本发明其他实施例中，壳体2011内嵌或者外包有磁场屏蔽装置(图中未示出)，如法拉第笼。本领域技术人员可以知晓的是，磁场屏蔽装置位于磁性件203外侧，以减少外界磁场对磁感元件20261的影响。
实施例三
加速度传感器
图5a为本发明实施例分析物检测系统唤醒模块包括加速度传感器的结构示意图。图5b为本发明实施例分析物检测装置唤醒模块包括加速度传感器的结构示意图。图5c为本发明实施例分析物检测装置唤醒模块包括加速度传感器的功能示意图。
在本发明实施例中，唤醒模块3026包括加速度传感器30261，加速度传感器30261可以灵敏地感应加速度等运动参数值，并相应地调整唤醒模块3026的电路状态。唤醒模块3026的触发条件为加速度传感器30261的运动参数变化。
发射器3023通过内部电路3024与电池3025连接，形成闭合回路，线路上连接有唤醒模块3026，电池3025通过唤醒模块3026(包括加速度传感器30261)向发射器3023供电。分析物检测装置302没有被安装到用户皮肤表面前，分析物检测装置302与辅助安装器301保持相对固定，为了将分析物检测装置传感器的体内部分30222刺入用户皮下，并且减轻刺入时的疼痛感，辅助安装模块3012采用弹射机构30121，如弹簧等弹性件，通过辅助针30122可以快速将体内部分30222刺入用户皮下。弹射机构30121在使用时产生瞬时较大的正向加速度a1，安装到用户皮肤表面后，受到皮肤的阻挡产生反向加速度a2，加速度传感器30261感应到上述两个加速度后，即可判定分析物检测装置302被安装到用户皮肤表面。
在本发明实施例中，分析物检测装置302被安装到用户皮肤表面前，唤醒模块3026处于开路状态，发射器3023处于休眠状态，分析物检测装置302以第一频率向外界设备发射信号。加速度传感器30261判定分析物检测装置302被安装到用户皮肤表面后，唤醒模块3026切换为闭路状态，发射器 3023进入工作状态，分析物检测装置302以第二频率向外界设备发射信号，待外界设备响应后建立通信，向外界设备传输分析物检测数据。
本领域技术人员可以理解的是，本专利中“第一频率”、“第二频率”均指信号的发射频率，以表征信号的发射间隔长短。
图6为本发明实施例分析物检测装置与外界设备通信连接的示意图。
在本发明实施例中，分析物检测装置102进入工作状态后即被激活，在与外界设备103建立通信前，发射第一信号，在与外接设备103建立通信后，发射第二信号。
在本发明实施例中，第一信号与第二信号的区别在于信号频率、信号类型、信号强度或/和信号格式。
在本发明一些实施例中，第一信号使用低功耗蓝牙(BLE)，而第二信号使用近场通信(NFC)；或者第一信号使用WiFi，而第二信号使用低功耗蓝牙(BLE)。
在本发明另一些实施例中，第一信号与第二信号为相同类型的信号，但它们的信号强度不同，例如，第一信号的信号强度弱于第二信号的信号强度。在本发明优选实施例中，通过设置第一信号和第二信号的强度，使得第一信号的有效范围为0～10m，第二信号的有效范围为0～10m。在本发明更优选实施例中，第一信号的有效范围为0～1m，更小的第一信号有效范围，便于外界设备103过滤错误的第一信号。
在本发明另一些实施例中，第一信号、第二信号具有不同的信号格式，例如第一信号数据包的通信连接状态标记为A，而第二信号数据包的通信连接状态标记为B。上述标记可以位于数据包的任一位置，例如数据包的包头，或者包体，等等。在本发明一个优选实施例中，设定数据包的包头作为通信连接状态标记位，在未建立通信连接状态下，分析物检测装置发送的第一信号数据包为A……，在已建立通信连接状态下，分析物检测装置发送的第二信号数据包为B……。在本发明另一个优选实施例中，设定数据包的多个标记位置作为通信连接状态标记，在未建立通信连接状态下，分析物检测装置发送的第一信号数据包为A…A…A…，在已建立通信连接状态下，分析物检测装置发送的第二信号数据包为B…B…B…。只要能将分析物检测装置的通信连接状态进行区分，数据包的标记位数量与格式不作限制。在本实施例中，通信连接状态标记A(B)在数据包中的形式可以是单字节，如0(1)，也可以是多字节，如000(111)，在此不作限制。
在本发明另一些实施例中，第一信号与第二信号具有不同的信号频率，例如第一信号为低频信号，而第二信号为高频信号，或者第一信号为高频信号，而第二信号为低频信号。
在本发明另一些实施例中，第一信号与第二信号的区别既在于信号格式，也在于信号强度，或者既在于信号格式，也在于信号强度，还在于信号频率，或者是其他信号区别形式的结合。信号的多种区别形式结合更利于外界设备将待连接的分析物检测装置区分出来。
只要能将第一信号区分于第二信号，可以采用包括但不限于上述技术方案，在此不作限制。无论第一信号、第二信号采用何种区分方式，第一信号、第二信号的特征均被预储存在外界设备103中。
图7为本发明实施例分析物检测装置与外界设备建立通信连接的流程示意图。参照图7，在本发明实施例中，用户需要建立分析物检测装置102与外界设备103间的通信连接时，先将外界设备103放置在分析物检测装置102的附近，并确认周围尽量不存在其他的分析物检测装置。用户启动外界设备103后，外界设备103搜索并识别附近信号，若外界设备103仅识别到一个第一信号，即可判断为该信号为待建立通信连接的分析物检测装置102发射的信号，并通过该信号的链路与分析物检测装置102建立通信连接，无需用户手动输入或者扫描分析物检测装置102的设备码，简化了建立通信连接的流程，避免用户输入或者扫描错误的设备码，提升了用户体验。
在本发明其他实施例中，分析物检测装置102与外界设备103建立通信连接前，外界设备103提示用户确认是否进行连接，以提高分析物检测装置102与外界设备103间通信连接的可靠性。
在本发明实施例中，若用户处于复杂环境中，即外界设备103识别到多个第一信号，或者多个第一信号和第二信号，外界设备103无法判断待建立通信连接的分析物检测装置102发射的第一信号，在这种情况下，外界设备103提示用户需要手动输入或者扫描待建立通信连接的分析物检测装置102的设备码，以便于与分析物检测装置102建立通信连接。
在本发明其他实施例中，当用户处于复杂环境中，外界设备103无法判断待建立通信连接的分析物检测装置102发射的第一信号，外界设备103提示用户更换操作地点，用户需要携带待建立通信连接的分析物检测装置102和外界设备103到其他地点，直至外界设备103仅识别到一个第一信号，即可判断为该信号为待建立通信连接的分析物检测装置102发射的信号，并通 过该信号的链路与分析物检测装置102建立通信连接，无需用户手动输入或者扫描分析物检测装置102的设备码，简化了建立通信连接的流程，避免用户输入或者扫描错误的设备码，提升了用户体验。
在本发明其他实施例中，若外界设备103在有效范围内没有识别到第一信号，则判断分析物检测装置102没有正常工作，此时外界设备103向用户发出告警或者故障提示，以提示用户检查或者更换分析物检测装置。
在本发明实施例中，外界设备103的提示可以是音频、视频或者振动等形式中的一种或者多种。在本发明一个实施例中，当外界设备103的提示是音频时，根据不同的提示需要，外界设备103发出长短不一和/或时间间隔不等的“嘀”提示音。在本发明另一个实施例中，当外界设备103的提示是视频时，根据不同的提示需要，在显示屏上显示不同的文字提示。在本发明再一个实施例中，当外界设备103的提示是振动时，根据不同的提示需要，外界设备103进行长短不一和/或时间间隔不等的振动。
在本发明一些实施例中，发射器1023包括天线10231等通信元件，天线10231由导电线圈构成，根据分析物检测装置302与外界设备通信的需求，需要对天线10231的导电线圈进行精确的设计和布局，以定制特定的电感、共振和损耗等特性。
由于天线的导电线圈是柔软的，需要依附于不易变形的基材，以防止其电感等特性在使用过程中发生改变。根据天线依附的基材材质，可分为陶瓷天线、PCB天线和FPC天线。陶瓷天线采用高低温结合烧制的方式，将导电线圈印在陶瓷基材上，成型后的陶瓷天线占用空间小、性能较好，但是带宽窄，比较难做到多频段；PCB天线是以PCB板为基材的天线，特定长度的导电线圈固定在PCB板上，成型后的PCB天线成本低，不需要单独组装天线，无需重复调试，但是PCB天线只适合单一频段，不同批次之间会有一定偏差，而且容易受到PCB板上电流的干扰；FPC天线是以FPC(Flexible Printed Circuit，柔性电路板)为基材，FPC天线具有较高的空间利用率，成本低，性能好，适合小型智能电子设备使用，但是使用前需要对每一个FPC天线进行单独的调试，而且安装不方便。根据使用需求，还有一些其他类型的天线，例如导电线圈依附的基材为塑料、胶布等。
为了减小分析物检测装置102的体积与重量，提升用户体验，可以从很多方面着手。
参考图2，在本发明一些实施例中，将特定长度的导电线圈印制在内部 电路1024的电路板上作为发射器1023的天线(图中未示出)，实现向外界设备发射信号，以及接收信号的功能。如果将内部电路1024上的天线转移印制在分析物检测装置102的其他部件上，可以减少内部电路1024的电路板体积，从而实现分析物检测装置102的小型化设计。
参照图8a，在本发明一些实施例中，将天线10231布置在电池1025的壳体外侧，内部电路1024的电路板无需再承载天线10231，可以缩小天线10231占用的电路板体积，从而可以实现分析物检测装置102的小型化设计。具体的，在本发明实施例中，利用LDS(Laser Direct Structuring，激光直接成型)、印刷或者壳体镶嵌等技术，将天线10231的导电线圈固定在电池1025的外壳表面，天线10231再通过导线(图中未示出)与发射器1023的控制电路连接。
在本发明一些实施例中，天线10231的发射和接收信号频率与导电线圈的电感高度敏感，而电池1025内部含有金属和其他高导电材料，可能在天线10231工作过程中出现涡流，这些涡流可能会降低导电线圈的电感，从而影响天线10231的工作性能，因此布置在电池1025外壳表面的导电线圈还需要采取降低涡流的措施，例如将电池1025的金属壳体换成PC、陶瓷、pp等可以减小涡流影响的材料。
在本发明一些实施例中，天线10231不局限于布置在图6a所示电池1025的上端面，还可以布置在电池1025的侧面、下端面，或者一部分布置在上端面，另一部分布置在侧面或者下断面，本领域技术人员可以理解的是，天线10231布置在电池1025的壳体外侧，可以包括电池1025壳体外侧的所有面。
参照图8b，在本发明一些实施例中，还可以将天线10231设置在分析物检测装置102的外壳1021上。具体的，在本发明实施例中，利用LDS、印刷或者壳体镶嵌等技术，将天线10231的导电线圈固定在外壳1021表面，优选的，将天线10231的导电线圈固定在外壳1021的内表面，可以防止外界脏污污染天线10231。
在本发明一些实施例中，天线10231可以位于上外壳10211，也可以位于下外壳10212，或者一部分位于上外壳10211，另一部分位于下外壳10212，以充分利用分析物检测装置102的内部空间。在本发明实施例中，当天线10231一部分位于上外壳10211，另一部分位于下外壳10212时，两部分导电线圈通过电线连接，形成三维天线，能够进一步提高对外壳内部空间的利用 率。
参照图8c，在本发明一些实施例中，还可以将天线10231设置在胶布104上。具体的，在本发明实施例中，利用LDS、印刷或者压合等技术，将天线10231的导电线圈固定在胶布104的表面或者夹层。优选的，将天线10231固定在胶布104的夹层中，可以防止外界赃物的污染。
在本发明一些实施例中，为了使天线10231能正常工作，可能要求胶布104适当增加一些硬度，以防止胶布104因用户肌肉蠕动而弯曲或者弯折，这样会影响布置在其上的天线10231的性能，甚至可能破坏天线10231。
在本发明一些实施例中，天线10231的导电线圈可以是如图6a-6c所示以卷曲的方式布置在基材上，也可以固定角度弯折、不固定角度弯折或者其他不规则的方式布置在基材上，只要天线10231能实现其以既定频率发射和接收通信信号的功能即可，其导电线圈在基材上的布置方式不作具体限定。
在本发明一些实施例中，天线10231的导电线圈可以布置在不同的基材上，例如，一部分布置在电池1025的壳体外侧，一部分布置在分析物检测装置102的外壳1021的内表面上，或者一部分布置在胶布104中，只要天线10231能实现其以既定频率发射和接收通信信号的功能即可，其导电线圈在基材上的布置位置不作具体限定。
在本发明一些实施例中，天线10231的可以是多段长度相同或者不同的导电线圈，并分别与发射器1023的控制电路电连接，形成多个天线，可以用来发射和接收不同频率的通信信号。
在本发明一些实施例中，多个天线通过发射器1023的控制电路的指令，可以实现同时发射或者接收通信信号，也可以错时发射或者接收通信信号。
在本发明一些实施例中，多个天线中的一个可以被设置为主天线，其他的天线为副天线。
在本发明一些实施例中，在分析物检测装置102处于休眠状态时，发射器1023的控制电路控制主天线以第一频率向外界发射信号，在分析物检测装置102转换为工作状态后，控制电路控制主天线以第二频率向外界发射信号。
在本发明一些实施例中，在分析物检测装置102处于休眠状态时，发射器1023的控制电路控制主天线以第一频率向外界发射信号，在分析物检测装置102转换为工作状态后，控制电路控制副天线以第二频率向外界发射信号。
在本发明一些实施例中，在分析物检测装置102处于休眠状态时，发射器1023的控制电路控制副天线以第一频率向外界发射信号，在分析物检测装 置102转换为工作状态后，控制电路控制主天线以第二频率向外界发射信号。
在本发明一些实施例中，在分析物检测装置102处于休眠状态时，发射器1023的控制电路控制主天线以第一信号强度向外界发射信号，在分析物检测装置102转换为工作状态后，控制电路控制主天线以第二信号强度向外界发射信号。
在本发明一些实施例中，在分析物检测装置102处于休眠状态时，发射器1023的控制电路控制主天线以第一信号强度向外界发射信号，在分析物检测装置102转换为工作状态后，控制电路控制副天线以第二信号强度向外界发射信号。
在本发明一些实施例中，在分析物检测装置102处于休眠状态时，发射器1023的控制电路控制副天线以第一信号强度向外界发射信号，在分析物检测装置102转换为工作状态后，控制电路控制主天线以第二信号强度向外界发射信号。在本发明实施例中，第一信号强度弱于第二信号强度。
在本发明一些实施例中，多个天线可以布置在同一非电路板基材上，也可以布置在不同非电路板基材上。
在本发明一些实施例中，多个天线可以是卷曲的方式布置在非电路板基材上，也可以固定角度弯折、不固定角度弯折或者其他不规则的方式布置在非电路板基材上。
用于实现唤醒模块1026功能的电路实施例。
根据上文所述，在分析物检测装置102没有被安装到用户皮肤表面前，为了尽可能延长电池1025的使用寿命，减少电池1025的能量消耗，分析物检测装置102处于休眠状态；分析物检测装置102通过辅助安装模块1012安装到用户皮肤表面后被唤醒，进入工作状态。图9为实现上述功能的唤醒模块1026功能的电路实施例。
在本发明一些实施例中，唤醒模块1026电路的电子构件包括感光元件10261、处理器10262、PMOS管(场效应晶体管)10263、第一电阻R1和第二电阻R2，各个电子构件按照电路实现逻辑进行可操作性连接，并由电池1025供电。具体的，感光元件10261的a端通过电阻R1与电池1025连接，处理器10262的c、d接口分别连接于电阻R1的两端，PMOS管10263的源极与电池1025连接，栅极与处理器10262的e接口连接，漏极与工作模块连接，这里工作模块是指至少包括天线10231等分析物检测装置102的必要工作构件的总称，在PMOS管10263的源极与栅极之间还连接有第二电阻R2， 感光元件10261的b端、处理器的g接口以及工作模块均接地。
在本发明实施例中，第一电阻R1为上拉电阻，在感光元件10261为开路的时候，使得处理器10262的d端为高电平；第二电阻R2为上拉电阻，在处理器10262处于深度休眠状态时，使得PMOS的栅极(e端)为高电平。
以上电子构件为唤醒模块1026电路的必要构件，本领域技术人员应当理解的是，为了更好地实现电路的功能，还可以增设稳压构件等辅助性构件，在此不作详细说明。
在本发明实施例中，工作模块还可以包括传感器检测电路、蜂鸣器、LED灯等电子构件。
在本发明实施例中，感光元件10261可以具体的为光电二极管、光电传感器、光敏电阻等。优选地，感光元件10261为光电二极管，光电二极管在未受到光照射时，具备良好的绝缘性能，而在受到光照射时，具备良好的导电性能。
在本发明实施例中，在使用前，分析物检测装置102固定于辅助安装器101内，辅助安装器101为分析物检测装置102提供稳定环境，例如稳定的光屏蔽环境，外界光束无法透过辅助安装器101照射到分析物检测装置102，以防止感光元件10261被触发。在使用后，分析物检测装置102与辅助安装器101分离，辅助安装器101不再为分析物检测装置提供光屏蔽环境，外界光束可照射在分析物检测装置102上，并进而照射在感光元件10261，感光元件10261被触发。
唤醒模块1026中各个构件的作用将在以下具体说明。
在本发明一些实施例中，感光元件10261在不受光束照射时，处于开路状态，处理器10262的c接口和d接口均处于高电平，可以通过设置第一电阻R1的阻值，例如10MΩ，使得处理器10262有微弱电流通过，即在分析物检测装置102出厂后处理器10262就上电，并处于深度休眠状态。同时，PMOS管10263的栅极通过第二电阻R2与电池1025连接，处于高电平状态，PMOS管10263处于开路，电池1025不能给工作模块供电。
在本发明一些实施例中，唤醒模块1026的电路中可以不包含第二电阻R2，处理器10262在处于深度休眠状态时，接口e为PMOS管10263的栅极提供高电平，使得PMOS管10263处于开路状态，待处理器10262转换为工作状态后，接口e为PMOS管10263的栅极提供低电平，使得PMOS管10263处于闭路状态。
在本发明一些实施例中，在分析物检测装置102出厂后，感光元件10261受到光束照射前，电池1025只向处理器10262提供微弱电流，这样在正式使用分析物检测装置102前，电子构件不会过多地消耗电池1025的电能，延长电池1025的使用寿命。
在本发明一些实施例中，用户使用辅助安装器101将分析物检测装置102安装在皮肤表面后，分析物检测装置102与辅助安装器101分离，感光元件10261受到光束照射，处于闭路状态，电流从a端流向b端，处理器10262的d接口电平降低，处理器10262转换为工作状态，此时处理器10262的e接口的电平降低，PMOS管10263的栅极降为低电平，PMOS管10263变更为闭路状态，工作模块可从电池1025获得电能，进入工作状态，发射器1023开始向外界发射信号。
在本发明一些实施例中，处理器10262一旦转换为工作状态后，其e接口被持续控制为低电平，这样可以使PMOS管10263持续导通，无论感光元件10261此后是否还能接受光束照射，电池1025可以持续为工作模块提供电能，即处理器10262在转换为工作状态后，感光元件10261的状态将不会影响唤醒模块1026的电路状态。
在本发明一些实施例中，工作模块由休眠状态进入工作状态指工作模块中的电子构件由未上电变更为上电。
在本发明一些实施例中，工作模块上电后，分析物检测装置102与外界设备建立通信连接前，天线10231以第一信号强度向外界发射信号，分析物检测装置102与外界设备建立通信连接后，天线10231以第二信号强度向外界发射信号，第一信号强度弱于第二信号强度。
在本发明一些实施例中，工作模块上电后，传感器检测电路开始工作，传感器1022被接通工作电流，可以检测用户体内分析物参数信息。
在本发明一些实施例中，工作模块上电后，分析物检测装置102与外界设备建立通信连接前，天线10231以第一频率向外界发射信号，分析物检测装置102与外界设备建立通信连接后，天线10231以第二频率向外界发射信号，第一频率低于第二频率。
在本发明一些实施例中，唤醒模块1026中的感光元件10261可被另一些状态切换构件代替，例如磁感元件、触控开关、加速度传感器等，在出厂后这些状态切换构件处于开路状态，使得处理器10262处于深度休眠状态，经过条件触发后这些状态切换构件变更为闭路状态，处理器10262变更为工作 状态，工作模块开始工作，相关电路实现过程在此不再描述。
综上所述，本发明实施例公开了一种节能分析物检测系统，在分析物检测装置安装前，处理器上电但处于深度休眠状态，发射器不向外发射信号，在分析物检测装置安装后，经过预定条件触发，处理器转换为工作状态，发射器开始向外界发射信号，能够节省电池的能量消耗，延长分析物检测装置的使用寿命。
虽然已经通过示例对本发明的一些特定实施例进行了详细说明，但是本领域的技术人员应该理解，以上示例仅是为了进行说明，而不是为了限制本发明的范围。本领域的技术人员应该理解，可在不脱离本发明的范围和精神的情况下，对以上实施例进行修改。本发明的范围由所附权利要求来限定。

Claims (9)

  1. 一种分析物检测系统，其特征在于，包括：
    辅助安装器，所述辅助安装器用于将分析物检测装置安装在用户皮肤表面；
    所述分析物检测装置至少包括发射器和传感器，所述发射器至少包括电池、唤醒模块和工作模块，所述唤醒模块将所述电池和所述工作模块电连接；
    其中，所述唤醒模块至少包括处理器、状态切换构件和场效应晶体管；
    其中，所述状态切换构件在触发前为开路，所述处理器上电并处于深度休眠状态，并使所述场效应晶体管开路，所述电池不向所述工作模块提供电能；在所述状态切换构件触发后为闭路，所述处理器转换为工作状态，并使所述场效应晶体管闭路，所述电池向所述工作模块提供电能；
    其中，在所述处理器转换为工作状态后，使所述场效应晶体管锁定为闭路，以使所述电池持续为所述工作模块提供电能。
  2. 根据权利要求1所述的分析物检测系统，其特征在于，所述状态切换构件为感光元件、磁感元件、触控开关或加速度传感器中的一种。
  3. 根据权利要求2所述的分析物检测系统，其特征在于，所述状态切换构件为光电二极管。
  4. 根据权利要求1所述的分析物检测系统，其特征在于，所述辅助安装器还用于为所述分析物检测装置提供稳定环境，在使用前，防止所述状态切换构件被触发。
  5. 根据权利要求4所述的分析物检测系统，其特征在于，所述辅助安装器为所述分析物检测装置提供光屏蔽环境。
  6. 根据权利要求5所述的分析物检测系统，其特征在于，在所述分析物检测装置与所述辅助安装器分离后，所述辅助安装器不再为所述分析物检测装置提供光屏蔽环境，所述状态切换构件被触发。
  7. 根据权利要求1所述的分析物检测系统，其特征在于，所述工作模块至少包括天线。
  8. 根据权利要求7所述的分析物检测系统，其特征在于，在所述工作模块被提供电能后，所述天线以第一频率或第一信号强度向外界发射信号。
  9. 根据权利要求1所述的分析物检测系统，其特征在于，所述传感器为葡萄糖传感器。
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Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023044889A1 (en) * 2021-09-27 2023-03-30 Medtrum Technologies Inc. Analyte detection system

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120078071A1 (en) * 2010-09-29 2012-03-29 Dexcom, Inc. Advanced continuous analyte monitoring system
US20220047178A1 (en) * 2019-01-03 2022-02-17 Northwestern University Ultra-low power, miniaturized electronic systems for monitoring physical parameters with wireless communication capabilities and applications of same
CN216257100U (zh) * 2021-09-27 2022-04-12 上海移宇科技股份有限公司 分析物检测装置安装单元
WO2023045566A1 (en) * 2021-09-27 2023-03-30 Medtrum Technologies Inc. Communication system of analyte detection device

Family Cites Families (85)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8465425B2 (en) * 1998-04-30 2013-06-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8688188B2 (en) * 1998-04-30 2014-04-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US7011630B2 (en) * 2001-06-22 2006-03-14 Animas Technologies, Llc Methods for computing rolling analyte measurement values, microprocessors comprising programming to control performance of the methods, and analyte monitoring devices employing the methods
US6917885B2 (en) * 2003-06-06 2005-07-12 Steris Inc. Method and apparatus for formulating and controlling chemical concentration in a gas mixture
US7723127B2 (en) * 2005-03-03 2010-05-25 Novx Systems Inc. Immunoassay with extended dynamic range
EP1960018A1 (en) * 2005-12-08 2008-08-27 Novo Nordisk A/S Medical system comprising a sensor device
US8140312B2 (en) * 2007-05-14 2012-03-20 Abbott Diabetes Care Inc. Method and system for determining analyte levels
US8346335B2 (en) * 2008-03-28 2013-01-01 Abbott Diabetes Care Inc. Analyte sensor calibration management
US7783442B2 (en) * 2007-10-31 2010-08-24 Medtronic Minimed, Inc. System and methods for calibrating physiological characteristic sensors
US9289168B2 (en) * 2008-12-29 2016-03-22 Medtronic Minimed, Inc. System and/or method for glucose sensor calibration
US8103456B2 (en) * 2009-01-29 2012-01-24 Abbott Diabetes Care Inc. Method and device for early signal attenuation detection using blood glucose measurements
US20100198034A1 (en) * 2009-02-03 2010-08-05 Abbott Diabetes Care Inc. Compact On-Body Physiological Monitoring Devices and Methods Thereof
US8110081B2 (en) * 2009-05-22 2012-02-07 Medical Graphics Corporation Oxygen sensor improvement method
CN105686807B (zh) * 2009-08-31 2019-11-15 雅培糖尿病护理公司 医疗设备
WO2011029035A2 (en) * 2009-09-04 2011-03-10 Johnson Controls Technology Company Secondary battery with improved acid destratification
US9089292B2 (en) * 2010-03-26 2015-07-28 Medtronic Minimed, Inc. Calibration of glucose monitoring sensor and/or insulin delivery system
US20110269164A1 (en) * 2010-04-30 2011-11-03 Arkray, Inc. Measuring Device, Measuring Method, and Program
EP3505064B8 (en) * 2011-09-23 2020-08-12 Dexcom, Inc. Systems and methods for processing and transmitting sensor data
CN102735284A (zh) * 2012-06-25 2012-10-17 青岛海信移动通信技术股份有限公司 一种传感器校准方法及装置
ES2759560T3 (es) * 2012-06-28 2020-05-11 Hoffmann La Roche Dispositivo de monitorización de al menos una función corporal de un usuario y procedimiento de fabricación del mismo
DE102012215883A1 (de) * 2012-09-07 2014-03-13 Robert Bosch Gmbh Energiespeicher mit Dichtigkeitsüberwachung
US20140188402A1 (en) * 2013-01-03 2014-07-03 Dexcom, Inc. Outlier detection for analyte sensors
US9931036B2 (en) * 2013-03-14 2018-04-03 Dexcom, Inc. Systems and methods for processing and transmitting sensor data
US10335075B2 (en) * 2013-03-14 2019-07-02 Dexcom, Inc. Advanced calibration for analyte sensors
EP2967452B1 (en) * 2013-03-15 2019-12-04 Abbott Diabetes Care Inc. Medical device data processing and communication methods and systems
EP3082574B1 (en) * 2013-12-16 2023-07-12 Dexcom, Inc. Systems and methods for monitoring and managing life of a battery in an analyte sensor system worn by a user
EP3114716A4 (en) * 2014-03-06 2017-07-26 UniCell LLC Battery cells and arrangements
CN104887242B (zh) * 2014-03-07 2018-08-28 上海移宇科技股份有限公司 分析物传感系统
EP2950058B1 (en) * 2014-05-28 2018-03-28 Axis AB Calibration data in a sensor system
RU2622880C2 (ru) * 2014-08-22 2017-06-20 Нокиа Текнолоджиз Ой Обработка информации датчика
US9332940B1 (en) * 2015-01-05 2016-05-10 Analog Devices, Inc. Compact wearable biological sensor modules
US9901293B2 (en) * 2015-02-24 2018-02-27 Senseonics, Incorporated Analyte sensor
DK3101571T3 (en) * 2015-06-03 2018-06-14 Hoffmann La Roche MEASUREMENT SYSTEM FOR MEASURING THE CONCENTRATION OF AN ANALYST WITH A SUBCUTAN ANALYST SENSOR
US10470660B2 (en) * 2015-09-10 2019-11-12 Dexcom, Inc. Transcutaneous analyte sensors and monitors, calibration thereof, and associated methods
EP3170451A1 (en) * 2015-11-19 2017-05-24 Roche Diabetes Care GmbH Sensor and sensor assembly for detecting an analyte in a body fluid
AU2016377480A1 (en) * 2015-12-21 2018-04-26 Dexcom, Inc. Continuous analyte monitoring system power conservation
US20170181672A1 (en) * 2015-12-28 2017-06-29 Medtronic Minimed, Inc. Sensor systems, devices, and methods for continuous glucose monitoring
US10327687B2 (en) * 2015-12-30 2019-06-25 Dexcom, Inc. System and method for factory calibration or reduced calibration of an indwelling sensor based on sensitivity profile and baseline model of sensors
EP3435866B1 (en) * 2016-03-31 2020-11-18 Dexcom, Inc. Analyte monitoring system
US20170290535A1 (en) * 2016-04-08 2017-10-12 Medtronic Minimed, Inc. Analyte sensor with indicators
EP3243434B1 (en) * 2016-05-13 2022-07-20 Roche Diabetes Care GmbH Analyte measurement system initialization method
US10172559B2 (en) * 2016-05-13 2019-01-08 Pacesetter, Inc. Implantable device header with embedded sensor and antenna
CN105962919A (zh) * 2016-06-18 2016-09-28 欧志洪 带有脉搏检测器的智能腕带表
ES2712051T3 (es) * 2016-06-23 2019-05-09 Hoffmann La Roche Procedimiento para una comunicación inalámbrica de datos entre un sistema de sensores y un receptor, un sistema para la comunicación inalámbrica de datos y un producto de programa informático
CA3152120A1 (en) * 2016-07-20 2018-01-25 Dexcom, Inc. System and method for wireless communication of glucose data
CN106137214A (zh) * 2016-08-12 2016-11-23 上海移宇科技股份有限公司 一种经皮分析物传感设备及其安装方法
AU2017311505B2 (en) * 2016-08-12 2020-07-02 Dexcom, Inc. Systems and methods for health data visualization and user support tools for continuous glucose monitoring
US10788445B2 (en) * 2017-03-17 2020-09-29 The University Of Akron Polymer electrolyte membrane fuel cell (PEMFC) sensor
WO2018185138A1 (en) * 2017-04-04 2018-10-11 Roche Diabetes Care Gmbh Body-wearable medical device
WO2018191467A1 (en) * 2017-04-12 2018-10-18 Roche Diabetes Care, Inc. Medical system
CN107219329B (zh) * 2017-04-13 2019-04-26 北京理工大学 低功耗气体检测方法及装置
WO2018204476A1 (en) * 2017-05-03 2018-11-08 Abbott Diabetes Care Inc. Systems, devices, and methods with duration-based adjustment of sensor data
HUE057712T2 (hu) * 2017-05-23 2022-05-28 Hoffmann La Roche Érzékelõrendszer és eljárás annak elõállítására
US10993646B2 (en) * 2017-08-18 2021-05-04 Abbott Diabetes Care Inc. Systems, devices, and methods related to the individualized calibration and/or manufacturing of medical devices
US20190120785A1 (en) * 2017-10-24 2019-04-25 Dexcom, Inc. Pre-connected analyte sensors
EP3700407A1 (en) * 2017-10-27 2020-09-02 Roche Diabetes Care GmbH A device and a method for detecting at least one analyte in a body fluid of a user
US11213230B2 (en) * 2017-12-13 2022-01-04 Medtronic Minimed, Inc. Optional sensor calibration in continuous glucose monitoring
CN109976997B (zh) * 2017-12-28 2022-12-27 北京京东尚科信息技术有限公司 测试方法和装置
AU2019263295A1 (en) * 2018-05-03 2020-09-17 Dexcom, Inc. Systems and method for activating analyte sensor electronics
US11656195B2 (en) * 2018-05-03 2023-05-23 Dexcom, Inc. Automatic analyte sensor calibration and error detection
JP2021522900A (ja) * 2018-05-04 2021-09-02 デックスコム・インコーポレーテッド 使い捨てベース内に位置するバッテリを有する分析物センサシステムに関するシステムおよび方法
CN108682755A (zh) * 2018-05-09 2018-10-19 广东弘捷新能源有限公司 纽扣电池及其制造方法
CN108968920A (zh) * 2018-07-12 2018-12-11 维沃移动通信有限公司 一种数据检测方法及电子设备
US20200330007A1 (en) * 2019-04-22 2020-10-22 Medtronic Minimed, Inc. Sensor with substrate including integrated electrical and chemical components and methods for fabricating the same
US11317867B2 (en) * 2019-04-23 2022-05-03 Medtronic Minimed, Inc. Flexible physiological characteristic sensor assembly
CN110162759A (zh) * 2019-05-22 2019-08-23 苏州高新区苏新立创环境科研技术有限公司 评估报告生成方法、存储介质及系统
EP3773208A4 (en) * 2019-06-04 2022-02-23 Waveform Technologies, Inc. SENSOR SIGNAL PROCESSING WITH KALMAN-BASED CALIBRATION
CN110208352A (zh) * 2019-06-24 2019-09-06 深圳硅基传感科技有限公司 葡萄糖传感器的出厂校准方法
EP3771412A1 (en) * 2019-08-02 2021-02-03 Bionime Corporation Physiological signal monitoring device
US20220218240A1 (en) * 2019-08-19 2022-07-14 Medtrum Technologies Inc. Sensing device
CN110764999A (zh) * 2019-09-06 2020-02-07 深圳壹账通智能科技有限公司 自动化测试方法、装置、计算机装置及存储介质
US11678820B2 (en) * 2019-09-10 2023-06-20 Ascensia Diabetes Care Holdings Ag Methods and apparatus for information gathering, error detection and analyte concentration determination during continuous analyte sensing
US11654235B2 (en) * 2019-09-12 2023-05-23 Medtronic Minimed, Inc. Sensor calibration using fabrication measurements
US11152664B2 (en) * 2019-12-24 2021-10-19 Anexa Labs Llc Compact electronics with optical sensors
CN113274014B (zh) * 2020-02-20 2024-05-14 上海移宇科技股份有限公司 分析物检测装置的安装单元及其安装方法
CN112771697B (zh) * 2020-03-09 2023-07-18 宁德新能源科技有限公司 电芯及具有该电芯的电池
AU2021236235A1 (en) * 2020-03-11 2022-08-18 Abbott Diabetes Care Inc. Graphical user interfaces for analyte monitoring systems
CN111781171A (zh) * 2020-06-12 2020-10-16 迈克医疗电子有限公司 体外检测样本中对象参数的测量方法、装置及设备
CN112120709A (zh) * 2020-09-27 2020-12-25 微泰医疗器械(杭州)有限公司 一种血糖监测装置
CN112568902A (zh) * 2020-12-15 2021-03-30 无锡轲虎医疗科技有限责任公司 一种基于血糖值的无创血糖校准方法
CN213583956U (zh) * 2020-12-16 2021-06-29 江西炳昶电池科技有限公司 一种具有双折边的聚合物电池结构
CN213660476U (zh) * 2020-12-23 2021-07-09 惠州市哈工新能源科技有限公司 一种快速充电的聚合物锂电池
CN112766067A (zh) * 2020-12-31 2021-05-07 杭州艾芯智能科技有限公司 3d人脸识别模组校准数据的获取方法、系统、计算机和存储介质
CN113219033B (zh) * 2021-04-30 2022-08-30 福州大学 一种电化学适配体传感器的免校正定量测量方法
CN113222663A (zh) * 2021-05-11 2021-08-06 北京京东振世信息技术有限公司 一种数据生成方法、装置、终端设备及存储介质

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120078071A1 (en) * 2010-09-29 2012-03-29 Dexcom, Inc. Advanced continuous analyte monitoring system
US20220047178A1 (en) * 2019-01-03 2022-02-17 Northwestern University Ultra-low power, miniaturized electronic systems for monitoring physical parameters with wireless communication capabilities and applications of same
CN216257100U (zh) * 2021-09-27 2022-04-12 上海移宇科技股份有限公司 分析物检测装置安装单元
WO2023045566A1 (en) * 2021-09-27 2023-03-30 Medtrum Technologies Inc. Communication system of analyte detection device
WO2023045432A1 (en) * 2021-09-27 2023-03-30 Medtrum Technologies Inc. System and method for realizing communication connection of analyte detection device
CN115868978A (zh) * 2021-09-27 2023-03-31 上海移宇科技股份有限公司 分析物检测系统及分析物检测装置控制方法

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