[go: up one dir, main page]

WO2020221331A1 - Émetteur et système de surveillance dynamique de glycémie avec alimentation électrique séparée, et procédé d'échantillonnage de signal - Google Patents

Émetteur et système de surveillance dynamique de glycémie avec alimentation électrique séparée, et procédé d'échantillonnage de signal Download PDF

Info

Publication number
WO2020221331A1
WO2020221331A1 PCT/CN2020/087965 CN2020087965W WO2020221331A1 WO 2020221331 A1 WO2020221331 A1 WO 2020221331A1 CN 2020087965 W CN2020087965 W CN 2020087965W WO 2020221331 A1 WO2020221331 A1 WO 2020221331A1
Authority
WO
WIPO (PCT)
Prior art keywords
battery
sensor
module
base
transmitter
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/CN2020/087965
Other languages
English (en)
Chinese (zh)
Inventor
钱成
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Suzhou Diascience Medical Co Ltd
Original Assignee
Suzhou Diascience Medical Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Suzhou Diascience Medical Co Ltd filed Critical Suzhou Diascience Medical Co Ltd
Priority to ES202190028U priority Critical patent/ES1282999Y/es
Publication of WO2020221331A1 publication Critical patent/WO2020221331A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Images

Classifications

    • 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 or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/14503—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue invasive, e.g. introduced into the body by a catheter or needle or using implanted 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 or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or 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 or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1473—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means 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 or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means using enzyme electrodes, e.g. with immobilised oxidase
    • A61B5/14865—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means using enzyme electrodes, e.g. with immobilised oxidase invasive, e.g. introduced into the body by a catheter or needle or using implanted sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/683—Means for maintaining contact with the body
    • A61B5/6832—Means for maintaining contact with the body using adhesives
    • A61B5/6833—Adhesive patches
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6848—Needles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6848—Needles
    • A61B5/6849—Needles in combination with a needle set
    • 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
    • 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
    • A61B2560/04—Constructional details of apparatus
    • A61B2560/0443—Modular apparatus
    • 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

Definitions

  • the application relates to a separate power supply dynamic blood glucose monitoring transmitter, system and signal sampling method, and belongs to the technical field of wearable medical devices.
  • the traditional dynamic blood glucose transmitter is mainly composed of three parts, a button battery, a circuit board and a plastic shell. Due to waterproof requirements and volume limitations, the button battery and circuit board are generally placed in the transmitter together, and the two are usually integrated into a plastic package. Therefore, the transmitter battery cannot be replaced, and the use time of the disposable sensor is generally 3-14 days. , It will be discarded after use. When the battery life is used up, the transmitter is basically unusable. From the perspective of cost, the cost of the transmitter's plastic casing and circuit board is much greater than the battery cost, and the lifetime of the transmitter's plastic casing and circuit board is much longer than the battery life. Therefore, this method will greatly waste circuit boards and plastic enclosures, increasing material costs and waste.
  • polymer rechargeable lithium batteries can improve the problem of cost waste, but polymer batteries will have the problem of loss. After considering the number of recharges, their life is still far lower than that of circuit boards and plastic enclosures, which cannot fundamentally solve the above problems.
  • polymer rechargeable batteries do not have standard products suitable for transmitters, and battery suppliers are usually required to provide non-standard supplies, which increases the difficulty of procurement.
  • a suitable method is adopted to separate the battery from the transmitter, so that the service life of the circuit board and the plastic shell is not limited by the battery life.
  • it is very meaningful to reduce costs and waste.
  • a smaller battery can be used to reduce the size of the system and improve the wearing experience.
  • the dynamic blood glucose transmitter calculates the blood glucose concentration by sampling the sensor current value. Therefore, the accuracy of the sampled sensor directly affects the accuracy of the blood glucose concentration calculation.
  • the wireless SOC module generally has a built-in ADC sampling circuit, and the accuracy of the circuit is usually marked. It is called about 10-12 bits, and the effective accuracy may be slightly lower than the nominal value. If higher accuracy is required, an expensive external ADC circuit needs to be added.
  • the technical problem to be solved in this application is to provide a high-precision dynamic blood glucose monitoring transmitter, system and signal sampling method with separate power supply in view of the above-mentioned shortcomings of the prior art.
  • a separate power supply dynamic blood glucose monitoring transmitter includes a transmitter and a sensor base device; the sensor base device includes a base and a tape, the base is located on the tape; the upper part of the base is an opening, and the base has a battery slot and a groove, so A battery and a battery cover are installed in the battery slot, a rotating seat is installed in the groove, and the rotating seat is hinged in the groove on one side of the battery slot.
  • the rotating seat has a silicone seat, and a pair of silicone seats are arranged in the silicone seat.
  • Conductive rubber through the silicone seat and the rotating seat is provided with a sensor, the sensor can pass through two conductive rubbers, the groove has an opening on one side of the battery slot, the tape is provided with a hole, the sensor can pass through the opening and the tape Hole;
  • the transmitter includes a plastic enclosure and a circuit board assembly, the plastic enclosure is closed on the base, the circuit board assembly is installed on the top of the plastic enclosure, the circuit board assembly has four conductive pins that can contact the battery Positive and negative electrodes and two conductive rubbers.
  • the silicone seat is provided with a first conductive rubber hole and a second conductive rubber hole, and the two conductive rubbers are respectively installed in the first conductive rubber hole and the second conductive rubber hole; in the silicone seat Two square holes are also provided, two conductive rubbers and two square holes are distributed in a straight line, and the sensor passes through the two conductive rubbers.
  • a semicircular hole is provided on both sides of the groove, a flexible extension rod is provided on both sides of the end of the rotating seat, and the outer side of the extension rod is provided with a cylindrical shaft, The cylindrical shaft is placed in a semicircular hole to rotate.
  • an electrode adapter is installed on the positive and negative poles of the battery, each electrode adapter is equipped with an electrode connector, and the battery cover is provided with two round holes, one The hole corresponds to an electrode connecting piece, and the electrode connecting piece passes through the round hole and is placed outside the battery cover.
  • the four conductive pins on the circuit board assembly are two battery guide pins and two rubber guide pins, the two battery guide pins are respectively connected to an electrode connector, and the two rubber guide pins are respectively connected to one Conductive rubber.
  • the end of the base has a base snap opening
  • the end of the plastic shell has an edge boss inserted into the snap opening of the base
  • the side of the plastic shell has a shell snap groove
  • the The inner side wall of the groove is provided with an elastic buckle which is inserted into the housing groove.
  • the edge of the battery slot has a sealing strip
  • the edge of the silicone seat has ribs.
  • Separate power supply dynamic blood glucose monitoring transmitter system including LC filter energy storage module, wireless SOC module, functional circuit power module, sensor excitation and conditioning module, ADC accuracy enhancement module, battery and sensor, the positive and negative electrodes of the battery are respectively passed through
  • the line is connected to the LC filter energy storage module.
  • connection line has a dual control switch, which can be connected to the Da end of the wireless SOC module or the functional circuit power supply Module, functional circuit power supply module is connected to the sensor excitation and conditioning module, the Db end of the wireless SOC module is also connected to the sensor excitation and conditioning module, the wireless SOC module has a built-in ADC module, the Dc end of the wireless SOC module and the built-in ADC module are both Connect the ADC accuracy enhancement module, the ADC accuracy enhancement module line is connected to the sensor excitation and conditioning module, the positive and negative poles of the sensor excitation and conditioning module are respectively connected to the sensor.
  • the beneficial effect of the present application is that the button battery is separated from the transmitter and integrated with the sensor.
  • the transmitter When not in use, the transmitter has not been installed on the sensor base. Therefore, the transmitter is in a power-off state and the button battery is not consumed.
  • the transmitter When in use, the transmitter is buckled into the sensor base, and the battery on the sensor base supplies power to the transmitter through an electrical connection. After use, remove the transmitter and discard the button battery together with the sensor. In this way, the button battery only needs to support the power of the sensor for one cycle. On the one hand, it will reduce the volume of the button battery, on the other hand, it will reduce the cost of the battery. In addition, since the transmitter can be reused, the cost will also be greatly reduced.
  • the newly designed ADC accuracy enhancement circuit can increase the sampling accuracy by 1 bit; the LC filter storage circuit can reduce the battery capacity (volume) on the one hand, and on the other hand can make the transmitter power supply more stable; and the wireless SOC module power supply Separate power supply from functional circuit power supply, effectively reducing power consumption. And designed a soft power-on method to make the transmitter work more stable and reliable.
  • Figure 1 is a schematic diagram of the structure of the application
  • Figure 2 is an exploded view of the launcher
  • Figure 3 is an exploded view of the sensor base device
  • Figure 4 is a sectional view of the silicone seat
  • Figure 5 is a schematic diagram of the structure of the base
  • Figure 6 is a schematic diagram of the battery cover structure
  • Figure 7 is a schematic diagram of the structure of the rotating seat and the silicone seat
  • FIG. 8 is a schematic diagram of the system modules of this application.
  • Figure 9 is a schematic diagram of a functional circuit module circuit
  • Figure 10 is a schematic diagram of soft power-on of the functional circuit power supply
  • Figure 11 is the sensor excitation and conditioning module circuit
  • Figure 12 is the ADC accuracy enhancement module circuit
  • Figure 13 is the LC filter energy storage module circuit
  • Figure 14 shows the wireless SOC module circuit.
  • the transmitter system is structured into two parts: the transmitter 200 and the sensor base device 300.
  • the sensor electrode 301 connected to the sensor base device 300 can be implanted into the recipient tissue through an auxiliary implant device.
  • the auxiliary implant device can be found in the published patent CN206424078U.
  • the hardware of the transmitter 200 includes a circuit board assembly 201 and a plastic housing 202.
  • the size of the transmitter is about 32mm*16mm*5mm. After being installed in the sensor base device 300, it is convenient to stick on the skin of the recipient and carry it with you.
  • the circuit board assembly 201 includes four conductive pins, and the conductive pins are generally conductive metal, preferably brass.
  • the conductive needle is drawn from the plastic shell 202 and is flush with the bottom surface of the plastic shell.
  • the conductive pins are respectively connected to the sensor S+S- and the battery V+V-.
  • the battery 304 in the sensor base 300 will supply power to the transmitter 200, and the transmitter 200 can convert the signal value measured from the sensor 301 into corresponding physiological parameters and send it to the user receiving end.
  • the plastic casing 202 completely wraps the circuit board components (except for the 4 conductive pins), which can achieve waterproof effect.
  • the plastic shell has an edge boss 2021 on the left side, and a shell slot 2022 on each side. When the transmitter is installed on the sensor base, the edge boss 2021 and the shell slot 2022 can fix the transmitter 200 on the base
  • the sensor base device 300 mainly includes a battery 304 and a sensor 301.
  • the battery 304 and the transmitter 200 are connected through electrical contacts V+ and V-.
  • the sensor 301 and the transmitter 200 are connected by electrical contacts S+S-.
  • the sensor base device 300 includes a sensor 301, a base 302, a tape 303, a battery 304, a battery adapter 305, an electrode connector 306, a battery cover 307, a waterproof sealing ring 308 of the battery connector, a rotating seat 309, a silicone seat 310 and conductive Rubber and so on 311.
  • the battery adapter 305 may be a metal component such as a nickel tape.
  • the battery adapter 305 is connected to the battery 304 and the battery connector 306 by welding or the like.
  • insulating paper is provided on the outside of the battery to prevent the positive and negative poles of the battery from conducting.
  • the battery connector 306 is placed on the battery adapter 305 and can be compressed by the installation of the battery cover 307.
  • the battery connector 306 is flexible and can be electrically connected to the transmitter.
  • the battery connector 306 may be a spring pin with a spring inside.
  • the base 302 has a waterproof sealing ring 308 on the surface, and the waterproof sealing ring can be made of elastic materials such as silica gel, TPE and TPU.
  • the waterproof sealing ring can be directly injection molded on the base, or it can be glued on the base later.
  • the waterproof sealing ring is trapezoidal or triangular, which can better place the transmitter and better waterproof. When combined with the bottom plane of the transmitter, it can play a waterproof role, and the waterproof level can reach IPX7.
  • the transmitter 200 In the unused state, the transmitter 200 has not been installed on the sensor base device 300. Therefore, the transmitter 200 is in a power-off state and the battery 304 is not consumed.
  • the transmitter 200 When in use, the transmitter 200 is buckled into the sensor base device 300, and the battery on the sensor base device 300 supplies power to the transmitter 200 through an electrical connection. After use, the transmitter is removed and the battery 304 is discarded together with the sensor.
  • the sensor 301 is implanted in the subcutaneous tissue of the living body and is configured to sense the original signal of the analyte.
  • the sensor 301 includes at least one working electrode and one reference electrode.
  • the working electrode and the reference electrode S+S- are electrically connected through the conductive rubber 311 and the battery guide pin 2011 and the rubber guide pin 2012 of the transmitter 200, respectively.
  • the base 302 on the one hand, is fixed on the recipient's skin by a non-woven fabric tape 303, and on the other hand, is configured to be fixedly connected to the transmitter 200.
  • the base 302 has a The battery compartment 3021 is configured to hold the battery 304.
  • the positive and negative electrodes of the battery are connected to the battery connector 306 through the battery adapter 305, and then lead to the outer surface of the base by the battery connector.
  • the base 302 has a base snap opening 3023 at the end.
  • the top of the opening is flat, and the bottom is provided with a certain angled slope.
  • the top surface is configured to cooperate with the edge boss 2021 of the transmitter 200 to limit the transmitter.
  • the bottom slope is easy to install the transmitter.
  • the base 302 has a groove 3024 on the right, and the groove is configured to place the rotating seat 309. After the sensor 301 is implanted, the rotating seat rotates clockwise to a certain angle, and finally fits with the bottom surface of the groove. There is an opening 3025 on the lower left side of the groove 3024 through which the sensor 301 can pass.
  • a semicircular hole 3026 is provided on both sides of the groove 3024, and the semicircular hole is matched with the cylindrical shaft 3092 of the rotating seat 309, so that the rotating seat can rotate along the axis of the hole.
  • An inclined surface is arranged above the semicircular hole 3026, and the inclined surface is convenient for the cylindrical shaft of the rotating seat to be clamped into the semicircular hole.
  • the elastic buckles are configured to cooperate with the housing slots 2022 on both sides of the transmitter.
  • the elastic buckles on both sides of the base are opened outward, and the transmitter is installed. After being in place, the elastic buckle retracts. The bottom surface of the elastic buckle is stuck with the transmitter card slot, restricting the transmitter from moving.
  • the battery cover 307 is configured to cooperate with the base 302 to fix the battery connector 306 and the battery 304.
  • a battery cover groove 3071 is provided in the middle of the battery cover 307 and is configured to accommodate the battery 304.
  • the two round holes 3073 on the top of the battery cover 307 can allow the elastic parts of the battery connector to pass through, so as to contact the transmitter contacts.
  • the rotating seat 309 provides support for the silicone seat 310 on it when it is not installed; on the other hand, when the installation is completed, it can rotate around the base to the installed state.
  • extension rods 3091 There are two extension rods 3091 on both sides of the rotating seat 309.
  • the extension rods have certain elasticity. When the extension rods are stressed, they can contract inward; after the force is cancelled, the extension rods can return to the original position.
  • the cylindrical shaft 3092 has an inclined surface on the side surface.
  • the inclined surface of the cylindrical shaft contacts and guides the inclined surface of the base.
  • the extension rod 3091 shrinks inwardly, the cylindrical shaft is clamped into the semicircular hole of the base, and the extension rod can be restored to the original position.
  • the degree of freedom of the rotating seat and the base part is limited, and the rotating seat can only rotate around the cylinder axis.
  • the silicone seat 310 on the one hand, is used to store the conductive rubber 311, provide deformation space for the conductive rubber and limit the conductive rubber; on the other hand, after the silicone seat is combined with the transmitter plane, it can play a waterproof role, and the waterproof level can reach IPX7 .
  • the silicone base 310 has a first conductive rubber hole 3101 and a second conductive rubber hole 3102 in the middle.
  • the round hole is used to place the conductive rubber 311.
  • conductive rubbers 311 There are two conductive rubbers 311. After implantation, the sensor 301 passes through the conductive rubber, and each conductive rubber is connected to the electrical contacts S+ and S- of the sensor 301 and the transmitter 200, so as to realize the sensor and Flexible electrical connection between transmitters. In addition to the role of electrical connection, conductive rubber maintains the position of the sensor through friction under pressure.
  • the silica gel seat 310 also has two square holes 3103. The purpose of the square hole is to reduce the resistance when the guide needle and the puncture needle are withdrawn from the silicone seat.
  • the silicone base 310 has a circle of trapezoidal or triangular ribs 3104 on the top, which can make the installation of the transmitter lighter and more waterproof.
  • the rotating base 309 and the base 302 are arranged at 45°, the hollow guide needle in the implanter passes through the rotating base 309 and the silicone base 310 in parallel, and passes through the first conductive rubber hole 3101 and the second conductive rubber hole 3102;
  • the hollow puncture needle is located in the guide needle, and its tip is configured to puncture the skin of the recipient.
  • the sensor 301 is a solid needle body made of soft material and is located in the puncture needle.
  • the battery on the base supplies power to the transmitter through the battery guide pin 2011 connected to V+V-.
  • the rubber guide pin 2012, the conductive rubber 311 and the sensor 301 connected to the transmitter S+S- form an electrical circuit.
  • the transmitter can measure the current value through the above-mentioned electrical circuit. And through the internal algorithm of the transmitter, the measured current value is converted into the recipient's blood sugar value. Then through the wireless transmission module, the blood glucose value is transmitted to the corresponding display device.
  • VDD is the supply voltage of the SOC
  • Da, Db, and Dc are the digital output pins of the SoC module.
  • the Da pin is configured to control the opening and closing of the switch S1 to control whether the battery supplies power to the functional circuit power module.
  • Db is configured to select the level of the sensor excitation circuit, so that the sensor excitation module can provide the sensor with high-level and low-level excitation voltage signals.
  • Dc is configured to inject a noise signal into the ADC accuracy enhancement module.
  • Ain1 and Ain2 are ADC inputs, configured to sample the conditioned and noise-injected sensor voltage output by the ADC accuracy enhancement module.
  • Q2 (corresponding to the switch S1 in Figure 1) realizes the function of the switch S1 module. Its gate VPER_SHDN (corresponding to the Da signal in Figure 1) is connected to Pin37 of the Bluetooth master chip U0 in the wireless SOC module circuit.
  • VPER_SHDN When VPER_SHDN is low, VBAT and V_PER are turned on.
  • the battery begins to supply power to functional circuits including sensor excitation and conditioning module circuits and ADC accuracy enhancement module circuits.
  • VPER_SHDN When VPER_SHDN is high, VBAT and V_PER are disconnected, and the functional circuits including sensor excitation and conditioning module circuit and ADC accuracy enhancement module circuit do not work, which can save power consumption.
  • the L1 and L2 inductors are mainly used to divide the digital circuit and the analog circuit. Since the analog circuit signal is a small signal sampling, the division of the digital and analog circuit can ensure that the analog signal is cleaner.
  • U1 is a precision reference power supply with an accuracy of one-thousandth.
  • the input is an analog power supply VCCA, and the output is a reference voltage signal VS_REF.
  • VS_REF is used as a reference level for applying sensor excitation.
  • C1, C2 are power filter capacitors.
  • This application uses soft power-on for the functional circuit power supply.
  • the wireless SOC module applies a PWM chopping waveform with a timing length of t to the gate of Q2, as shown in Figure 10, the PWM duty cycle gradually increases At this time, the output voltage of the analog switch is slowly rising, and the current will maintain a small value range during the voltage rise.
  • the current size is related to the PWM period and duty cycle.
  • the power-on current using the PWM soft power-on method can be adjusted according to the PWM duration, duty cycle and PWM period, so this method is used.
  • R1, R2, R3, R4, R5, R6, Q1, U5 constitute a sensor excitation circuit, and the gate of Q1 is connected to Pin39 of the Bluetooth master chip U0 in the wireless soc module.
  • the sensor excitation circuit output VS+ is connected to the positive pole of the sensor through the transmitter electrical contact S+.
  • VS_REF is the output of the precision reference voltage source in the functional circuit power module. The calculation relationship between output VS+ and VS_REF is as follows,
  • R4//R5 represents the equivalent resistance of R4 and R5 in parallel
  • R7, R8, C5, U6 form a conditioning circuit, which is essentially an I-V arithmetic circuit, whose main function is to convert the current signal flowing into VS- into a voltage signal ADC_GLU for the ADC module to convert into a digital signal.
  • Pin3 of U6 is connected to the negative pole of the sensor through the transmitter electrical contact S-. According to the operational amplifier analysis method, it can be known that the voltage of S- should be equal to VS_REF.
  • C3 and C39 are U5 and U6 power decoupling capacitors.
  • C8 is a filter capacitor, which controls the noise bandwidth of the current signal.
  • ADC_GLU VS_REF+I0*R 8
  • R8 is preferably 1M ⁇ .
  • the accuracy of the built-in analog-to-digital conversion circuit ADC in the main control chip is fixed and limited, and sometimes cannot meet the application requirements.
  • the usual solution is to use an external ADC chip, but the off-chip ADC is usually more expensive.
  • this example invented the ADC accuracy enhancement circuit module.
  • the ADC accuracy enhancement circuit adopts a noise injection method, which can increase the sampling accuracy by 1 bit based on the fixed accuracy of the built-in ADC of the main control chip of the wireless SOC module.
  • the circuit for injecting the noise signal is implemented by an addition circuit, and each sampling requires an addition circuit.
  • U8, R13, R14, R15, R16 form a precision enhancement circuit for VS_REF.
  • U9, R17, R18, R19, and R20 form a precision enhancement circuit for ADC_GLU.
  • Each ADC precision enhancement circuit structure is the same.
  • the precision enhancement circuit is filtered by a post-filter circuit composed of R9R10C8C9C10 and outputs ADC_R and ADC_G connected to the built-in ADC pins Pin41 and Pin42 of the Bluetooth master chip U0 in the wireless SOC module for analog-to-digital conversion.
  • Bit11 (corresponding to the Dc signal in Figure 1) is the noise injection signal, which is connected to Pin38 of U0. The injected signal is only 3V high and low level 0V.
  • the ADC standard conversion accuracy of the Bluetooth master chip without oversampling is 10 bits, and the reference voltage is calculated as 1 (100%), and its accuracy is
  • the result register is a 12-bit register, and the high bit of the result is aligned with the result register.
  • Table 1 and Table 2 give the calculation process of accuracy enhancement after signal injection.
  • the LC filter energy storage circuit can choose a button battery with a smaller capacity (volume), which effectively reduces the impact of the pulse current of the wireless SOC module on the battery voltage when a radio frequency event occurs, and makes the transmitter power supply more stable.
  • a battery with a smaller capacity (volume) can be selected to effectively reduce the impact of the pulse current of the wireless SOC module on the battery voltage when a radio frequency event occurs, so that the power supply of the transmitter is more stable, and a smaller capacity (volume) can be selected accordingly battery;
  • V+V- is connected to the positive and negative electrodes of the battery, and VDD_NRF supplies power to the Bluetooth master chip in the wireless SOC module.
  • L6, C34, C35, C36 and C37 constitute the LC filter tank circuit. Because the discharge capacity of the battery is related to the capacity, the conventional, generally small-capacity CR series button battery pulse discharge capacity is about 5mA, and the Bluetooth chip has a current load of up to 12mA or more when a radio frequency event occurs (when wirelessly sending or receiving data) , Far exceeds the pulse discharge capacity of the battery.
  • the pulse discharge capacity of the battery When the pulse discharge capacity of the battery is insufficient, the voltage at both ends of the battery will be pulled down. When the voltage is too low, the Bluetooth main control chip will be reset and the entire system will be under-powered. On the other hand, the repeated pulse current will also cause damage to the battery itself, that is, the pulse current will make the actual operating capacity of the battery much smaller than the nominal capacity.
  • this example adds an inductance capacitor filter energy storage circuit.
  • C34, C35, C36 and C37 mainly function as energy storage.
  • the entire circuit power consumption Very small, so the battery charges the capacitor more than the capacitor discharges the system circuit, and the excess energy is stored in the capacitor.
  • the pulse current required by the system circuit is first obtained from the capacitor, so the battery does not need to provide pulse current, so that the battery is in a relatively smooth discharge state throughout the working cycle, effectively suppressing the voltage drop event, and Prevent the pulse current from damaging the battery.
  • the inductor L6 mainly suppresses the current amplitude of the battery charging the capacitor, because the pulse current is a high-frequency characteristic current, and the inductor L6 can present a large impedance characteristic to high frequencies.
  • L6 can make the battery discharge priority over the battery discharge, that is, give priority to using the power stored in the capacitor.
  • the wireless SOC module circuit preferably uses the Bluetooth chip U0 as the main control chip.
  • the power supply of the wireless SOC module and the power supply of the functional circuit are separated, and each is independently powered.
  • the functional circuit power supply is mainly for the sensor excitation and conditioning circuit, and the accuracy enhancement circuit. Use the method of separate power supply, according to the principle of who works and who supplies power. When the functional circuit does not need to work, it does not consume battery power, effectively reducing power consumption.
  • a soft power-on method is designed, which effectively suppresses the pulse current amplitude at the moment of power-on and makes the transmitter work more reliable.
  • Capacitors C27, C28 and crystal Y1 provide a high-frequency clock source for the Bluetooth chip, and crystal Y1 is preferably 16MHz.
  • Capacitors C21, C22 and crystal Y2 provide a low-frequency clock source for the Bluetooth chip, and crystal Y2 is preferably 32.768kHz.
  • DV, DIO, DCK, DG are simulation ports, which are configured as simulation and programming programs.
  • C23, C24, C25, C26, C29, C30 and C33 are decoupling capacitors for the Bluetooth chip power supply.
  • L4, C31 and antenna ANT1 form a Bluetooth radio frequency circuit, which is configured to modulate wireless signals.
  • Pin37 of U0 is connected to the gate of the switch S1 circuit Q2, and is configured to control the on-off of the power supply of the functional circuit.
  • the output is low, and the functional circuit is in a non-working state at this time, so as to save power consumption.
  • Pin41 and Pin42 of U0 are the sensor current sampling signals that have passed the ADC accuracy enhancement module circuit, and are configured to calculate the blood glucose concentration.
  • Pin6 of U0 is connected to the positive electrode of the battery, collects the voltage value of the battery, and is configured to calculate the battery power according to the voltage-power curve of the battery.
  • Pin39 of U0 is connected to the gate of Q1 in the sensor excitation and conditioning module circuit, and is configured to select the level of excitation applied by the sensor.
  • a mosfet can be used to apply two-level excitation to the sensor.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Molecular Biology (AREA)
  • Biomedical Technology (AREA)
  • General Health & Medical Sciences (AREA)
  • Pathology (AREA)
  • Veterinary Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
  • Optics & Photonics (AREA)
  • Chemical & Material Sciences (AREA)
  • Emergency Medicine (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Urology & Nephrology (AREA)
  • General Chemical & Material Sciences (AREA)
  • Immunology (AREA)
  • Hematology (AREA)
  • Cell Biology (AREA)
  • Microbiology (AREA)
  • Biotechnology (AREA)
  • Food Science & Technology (AREA)
  • Medicinal Chemistry (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • General Physics & Mathematics (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention concerne un émetteur et un système de surveillance dynamique de glycémie avec une alimentation électrique séparée, et un procédé d'échantillonnage de signal. L'émetteur de surveillance de glycémie dynamique comprend structurellement un émetteur et un dispositif de base de capteur, le dispositif de base de capteur étant composé d'une base et d'une bande adhésive ; la base est pourvue intérieurement d'une fente de batterie et d'une rainure ; une batterie est montée dans la fente de batterie ; une base rotative est montée dans la rainure ; un côté de la base rotative est articulé dans la rainure ; la base rotative est pourvue à l'intérieur d'une base en silicone ; la base en silicone est pourvue à l'intérieur d'une paire de parties en caoutchouc conducteur ; l'émetteur comprend un ensemble carte de circuit imprimé ; et l'ensemble carte de circuit imprimé est pourvu de quatre broches conductrices, d'une électrode positive et d'une électrode négative pouvant entrer en contact avec la batterie, et de deux parties de caoutchouc conducteur. Par rapport à l'état de la technique, dans la présente invention, une pile bouton peut être séparée de l'émetteur et intégrée à un capteur ; lorsqu'il n'est pas utilisé, l'émetteur n'est toujours pas monté sur une base de capteur, et ainsi, l'émetteur est dans un état hors tension, de telle sorte que la puissance de la pile bouton n'est pas consommée ; et lors de l'utilisation, l'émetteur est ajusté par encliquetage dans la base de capteur, de telle sorte que la batterie sur la base de capteur fournit de l'énergie à l'émetteur par l'intermédiaire d'une connexion électrique.
PCT/CN2020/087965 2019-04-30 2020-04-30 Émetteur et système de surveillance dynamique de glycémie avec alimentation électrique séparée, et procédé d'échantillonnage de signal Ceased WO2020221331A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
ES202190028U ES1282999Y (es) 2019-04-30 2020-04-30 Transmisor Dinámico de Monitorización de la Glucosa en Sangre con una Fuente de Alimentación Independiente

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CN201910366312.7 2019-04-30
CN201910366312.7A CN109998560B (zh) 2019-04-30 2019-04-30 分离供电动态血糖监测发射器、系统及信号采样方法

Publications (1)

Publication Number Publication Date
WO2020221331A1 true WO2020221331A1 (fr) 2020-11-05

Family

ID=67175518

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2020/087965 Ceased WO2020221331A1 (fr) 2019-04-30 2020-04-30 Émetteur et système de surveillance dynamique de glycémie avec alimentation électrique séparée, et procédé d'échantillonnage de signal

Country Status (6)

Country Link
CN (1) CN109998560B (fr)
AT (1) AT17919U1 (fr)
CZ (1) CZ35661U1 (fr)
DE (1) DE202020005637U1 (fr)
ES (1) ES1282999Y (fr)
WO (1) WO2020221331A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP4312761A2 (fr) * 2021-03-30 2024-02-07 Ascensia Diabetes Care Holdings AG Dispositifs et systèmes de surveillance continue d'analytes ayant une unité de transmission sans fil réutilisable à longue durée de vie et leurs procédés d'application

Families Citing this family (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN109998560B (zh) * 2019-04-30 2023-12-22 苏州百孝医疗科技有限公司 分离供电动态血糖监测发射器、系统及信号采样方法
AU2020294357B2 (en) * 2019-08-02 2022-11-24 Bionime Corporation Physiological signal monitoring device
TWI735137B (zh) * 2019-08-02 2021-08-01 華廣生技股份有限公司 生理訊號傳感裝置
US11737689B2 (en) 2019-08-02 2023-08-29 Bionime Corporation Physiological signal monitoring device
EP3771425A1 (fr) 2019-08-02 2021-02-03 Bionime Corporation Dispositif d'insertion pour un biocapteur et son procédé d'insertion
US11896804B2 (en) 2019-08-02 2024-02-13 Bionime Corporation Insertion device for a biosensor and insertion method thereof
CA3104716C (fr) 2019-08-02 2023-07-18 Bionime Corporation Dispositif de surveillance de signal physiologique
CN112294305B (zh) * 2019-08-02 2024-07-02 华广生技股份有限公司 生理信号传感装置
US12478328B2 (en) 2019-08-02 2025-11-25 Bionime Corporation Physiological signal monitoring device
EP4017357A4 (fr) * 2019-08-19 2023-04-19 Medtrum Technologies Inc. Dispositif de détection
WO2021164181A1 (fr) * 2020-02-20 2021-08-26 Medtrum Technologies Inc. Unité de montage d'un dispositif de détection d'analyte et son procédé de montage
EP4106627A4 (fr) * 2020-02-20 2024-05-01 Medtrum Technologies Inc. Dispositif de détection d'analyte hautement intégré
WO2022252002A1 (fr) * 2021-05-31 2022-12-08 上海移宇科技股份有限公司 Dispositif de détection d'analytes de liquides organiques
CN115474931B (zh) * 2021-05-31 2025-10-31 上海移宇科技股份有限公司 体液分析物检测器件
CN115684597A (zh) * 2021-07-31 2023-02-03 华为技术有限公司 监测装置及监测设备
CN113951879B (zh) * 2021-12-21 2022-04-05 苏州百孝医疗科技有限公司 血糖预测方法和装置、监测血糖水平的系统
CN114366088B (zh) * 2021-12-23 2024-06-25 微泰医疗器械(杭州)股份有限公司 一种植入式生物传感器递送系统及植入激活方法
CN114711765B (zh) * 2022-06-07 2022-10-14 苏州百孝医疗科技有限公司 连续分析物浓度监测系统
CN116687396A (zh) * 2023-03-02 2023-09-05 镜像生命(苏州)科技有限公司 一种血糖浓度监测装置
TWD231831S (zh) * 2023-03-15 2024-06-21 華廣生技股份有限公司 臺中市南區大慶街2段100號 (中華民國) 用於生理監測裝置的拆分器之部分
WO2025152017A1 (fr) * 2024-01-16 2025-07-24 上海移宇科技有限公司 Dispositif de détection d'analytes de liquides organiques
CN120000214B (zh) * 2025-03-25 2025-10-31 歌尔股份有限公司 血糖检测装置

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130267809A1 (en) * 2004-07-13 2013-10-10 Dexcom, Inc. Analyte sensor
CN106461638A (zh) * 2014-04-11 2017-02-22 安晟信医疗科技控股公司 电池供电式生物传感器仪表的无线发射器适配器及设置方法
CN108078570A (zh) * 2016-11-21 2018-05-29 南通九诺医疗科技有限公司 一种内置加速度传感器的动态血糖监测电路及其控制方法
WO2018222011A1 (fr) * 2017-06-02 2018-12-06 주식회사 아이센스 Ensemble applicateur de capteur pour système de surveillance du glucose en continu
CN109998555A (zh) * 2019-04-30 2019-07-12 苏州百孝医疗科技有限公司 一种受体生理参数测量系统
CN109998560A (zh) * 2019-04-30 2019-07-12 苏州百孝医疗科技有限公司 分离供电动态血糖监测发射器、系统及信号采样方法

Family Cites Families (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7301308B2 (en) * 2001-11-02 2007-11-27 Aker Wade Power Technologies, Llc Fast charger for high capacity batteries
US9414777B2 (en) * 2004-07-13 2016-08-16 Dexcom, Inc. Transcutaneous analyte sensor
US9107690B2 (en) * 2007-12-03 2015-08-18 Covidien Ag Battery-powered hand-held ultrasonic surgical cautery cutting device
CN102065764A (zh) * 2008-03-17 2011-05-18 艾森斯公司 分析物传感器子组件、用于插入与之关联的分析物传感器的方法和装置
US9931065B2 (en) * 2012-04-04 2018-04-03 Dexcom, Inc. Transcutaneous analyte sensors, applicators therefor, and associated methods
US9788354B2 (en) * 2013-03-14 2017-10-10 Dexcom, Inc. Systems and methods for processing and transmitting sensor data
CN103750819B (zh) * 2013-12-25 2016-08-31 浙江凯立特医疗器械有限公司 可控制植入角度的皮下组织内传感器装置
US10305298B2 (en) * 2014-03-17 2019-05-28 Glx Power Systems, Inc. Method and apparatus for creating a dynamically reconfigurable energy storage device
CN105024582B (zh) * 2015-07-27 2018-08-21 江苏大学 一种新型两级式双向储能变流器控制系统及其控制方法
US20170290535A1 (en) * 2016-04-08 2017-10-12 Medtronic Minimed, Inc. Analyte sensor with indicators
CN206424078U (zh) 2016-11-09 2017-08-22 南通九诺医疗科技有限公司 生物传感器电极弹力式植入装置
CN106859662A (zh) * 2017-02-17 2017-06-20 宋琳 一种可充电式多功能血糖监测仪
US10819148B2 (en) * 2017-08-18 2020-10-27 Google Llc Smart-home device switching circuitry with integrated power stealing control
CN210056040U (zh) * 2019-04-30 2020-02-14 苏州百孝医疗科技有限公司 分离供电动态血糖监测发射器及其系统

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130267809A1 (en) * 2004-07-13 2013-10-10 Dexcom, Inc. Analyte sensor
CN106461638A (zh) * 2014-04-11 2017-02-22 安晟信医疗科技控股公司 电池供电式生物传感器仪表的无线发射器适配器及设置方法
CN108078570A (zh) * 2016-11-21 2018-05-29 南通九诺医疗科技有限公司 一种内置加速度传感器的动态血糖监测电路及其控制方法
WO2018222011A1 (fr) * 2017-06-02 2018-12-06 주식회사 아이센스 Ensemble applicateur de capteur pour système de surveillance du glucose en continu
CN109998555A (zh) * 2019-04-30 2019-07-12 苏州百孝医疗科技有限公司 一种受体生理参数测量系统
CN109998560A (zh) * 2019-04-30 2019-07-12 苏州百孝医疗科技有限公司 分离供电动态血糖监测发射器、系统及信号采样方法

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
HAN, CHAO ET AL.: "Method to Improve Precision of ADC", JOURNAL OF JILIN UNIVERSITY (INFORMATION SCIENCE EDITION, vol. 34, no. 3, 31 May 2016 (2016-05-31), pages 396 - 400, XP055751152, ISSN: 1671-5896, DOI: 10.19292/j.cnki.jdxxp.2016.03.015 *

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP4312761A2 (fr) * 2021-03-30 2024-02-07 Ascensia Diabetes Care Holdings AG Dispositifs et systèmes de surveillance continue d'analytes ayant une unité de transmission sans fil réutilisable à longue durée de vie et leurs procédés d'application
US12290334B2 (en) 2021-03-30 2025-05-06 Ascensia Diabetes Care Holdings Ag Continuous analyte monitoring devices and systems having a long-life reusable wireless transmitter unit and application methods therefor

Also Published As

Publication number Publication date
ES1282999Y (es) 2022-02-25
ES1282999U (es) 2021-11-29
CN109998560A (zh) 2019-07-12
AT17919U1 (de) 2023-07-15
DE202020005637U1 (de) 2022-01-07
CZ35661U1 (cs) 2021-12-14
CN109998560B (zh) 2023-12-22

Similar Documents

Publication Publication Date Title
WO2020221331A1 (fr) Émetteur et système de surveillance dynamique de glycémie avec alimentation électrique séparée, et procédé d'échantillonnage de signal
CN210056040U (zh) 分离供电动态血糖监测发射器及其系统
CN110337267B (zh) 生物信号测量装置
US11677254B2 (en) Automatic activation of continuous glucose monitoring (CGM) transmitter
US11497437B2 (en) Sleep monitoring circuit and sleep monitoring apparatus
CN204049971U (zh) 一种无线智能止鼾器
CN104997503A (zh) 一种便携式心电图监测装置
CN101584909B (zh) 一种便携式无创神经原性膀胱治疗仪
CN105266795A (zh) 动态心电信号采集装置
CN218793565U (zh) 一种带充电仓的遥控按摩仪
CN115844397A (zh) 动态血糖仪
CN201516033U (zh) 指夹式血氧仪的电源软开关电路
CN105358216A (zh) 用于具有非可再充电电池的可植入医疗装置的电力结构
McAdams et al. Low-cost, implantable wireless sensor platform for neuromodulation research
JP6876464B2 (ja) 生体信号計測装置
CN209472652U (zh) 带心电检测功能的手机保护壳
CN209529134U (zh) 基于自动控制开关的动态血糖仪
Hackworth Design, optimization, and implementation of a volume conduction energy transfer platform for implantable devices
CN210873750U (zh) 按摩贴
CN210158886U (zh) 手足康复治疗仪
CN214761161U (zh) 电子听诊器用信号处理电路
CN208910241U (zh) 一种心谱贴
CN218685740U (zh) 一种便携式脉冲按摩仪
CN222426665U (zh) 微型电针仪
CN109905519A (zh) 一种带心电检测功能的手机保护壳

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 20798185

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 20798185

Country of ref document: EP

Kind code of ref document: A1