CN109998560B - Separated power supply dynamic blood glucose monitoring transmitter, system and signal sampling method - Google Patents

Separated power supply dynamic blood glucose monitoring transmitter, system and signal sampling method Download PDF

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Publication number
CN109998560B
CN109998560B CN201910366312.7A CN201910366312A CN109998560B CN 109998560 B CN109998560 B CN 109998560B CN 201910366312 A CN201910366312 A CN 201910366312A CN 109998560 B CN109998560 B CN 109998560B
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China
Prior art keywords
module
sensor
circuit
battery
adc
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CN201910366312.7A
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CN109998560A (en
Inventor
钱成
肖林春
卞庆祥
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Diascience Medical Co Ltd
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Diascience Medical Co Ltd
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Priority to CN201910366312.7A priority Critical patent/CN109998560B/en
Publication of CN109998560A publication Critical patent/CN109998560A/en
Priority to DE202020005637.5U priority patent/DE202020005637U1/en
Priority to ATGM50219/2021U priority patent/AT17919U1/en
Priority to PCT/CN2020/087965 priority patent/WO2020221331A1/en
Priority to ES202190028U priority patent/ES1282999Y/en
Priority to CZ202139300U priority patent/CZ35661U1/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—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
    • A61B5/14503—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 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, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1468—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 chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1473—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 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, 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
    • A61B5/14865—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 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

Abstract

The invention discloses a separated power supply dynamic blood glucose monitoring transmitter, a system and a signal sampling method, structurally comprising a transmitter and a sensor base device; the sensor base device is divided into a base and an adhesive tape, a battery groove and a groove are formed in the base, a battery is installed in the battery groove, a rotating seat is installed in the groove, one side of the rotating seat is hinged in the groove, a silica gel seat is arranged in the rotating seat, a pair of conductive rubbers is arranged in the silica gel seat, the transmitter comprises a circuit board assembly, four conductive pins are arranged on the circuit board assembly, and the positive electrode and the negative electrode of the battery can be contacted with the two conductive rubbers. Compared with the prior art, the button battery can be separated from the transmitter and integrated with the sensor, and when the button battery is not used, the transmitter is not installed on the sensor base, so that the transmitter is in a power-off state, the button battery does not consume power, and when the button battery is used, the transmitter is buckled on the sensor base, and the battery on the sensor base is electrically connected to supply power for the transmitter.

Description

Separated power supply dynamic blood glucose monitoring transmitter, system and signal sampling method
Technical Field
The invention relates to a separated power supply dynamic blood glucose monitoring transmitter, a system and a signal sampling method, and belongs to the technical field of wearable medical instruments.
Background
The traditional dynamic blood sugar transmitter mainly comprises three parts, namely a button cell, a circuit board and a plastic package shell. Because of the waterproof requirement and the volume limitation, the button battery and the circuit board are generally placed in the emitter together, and the button battery and the circuit board are generally integrally molded, so that the emitter battery is not replaceable, the use time of the disposable sensor is generally different in 3-14 days, the disposable sensor is abandoned after the use, and the emitter is basically not reusable after the service life of the battery is finished. From the cost perspective, the cost of the plastic package shell and the circuit board of the transmitter is far greater than the cost of the battery, and the service lives of the plastic package shell and the circuit board of the transmitter are also far greater than the service life of the battery. Therefore, the circuit board and the plastic package shell can be wasted greatly, and the material cost and the waste are increased.
The polymer rechargeable lithium battery can improve the problem of cost waste, but the polymer battery has the problem of loss, and the service life of the polymer battery is still far lower than that of a circuit board and a plastic package shell after the charging times are considered, so that the problem can not be fundamentally solved. In addition to the lack of standard products for transmitters, polymer rechargeable batteries often require non-standard supplies from the battery suppliers, increasing the difficulty of purchase.
In addition, in order to effectively utilize the service life of the transmitter circuit board and the plastic package shell, the cost and the waste are reduced. Button cells with slightly larger volumes (larger amounts of electricity) are often selected, so that the emitter cannot be designed to have smaller volumes, and wearing experience is reduced.
In order to solve the problems, a proper mode is adopted to separate the battery from the emitter, so that the service lives of the circuit board and the plastic package shell are not limited by the service lives of the battery, the circuit board and the plastic package shell are very significant in reducing cost and waste, and on the other hand, the battery with smaller volume can be selected, the system volume is reduced, and the wearing experience is improved.
In addition, the dynamic blood glucose transmitter calculates the blood glucose concentration by sampling the sensor current value, so the accuracy of the sampled sensor directly influences the accuracy of calculating the blood glucose concentration, and a built-in ADC sampling circuit is generally arranged in the wireless SOC module, the circuit accuracy is usually marked as about 10-12 bits, and the effective accuracy can be slightly lower than the nominal value. If higher accuracy is desired, expensive external ADC circuitry is added.
Disclosure of Invention
The invention aims to solve the technical problem of providing a high-precision dynamic blood glucose monitoring transmitter, a system and a signal sampling method with separate power supply aiming at the defects of the prior art.
In order to solve the technical problems, the invention adopts the following technical scheme:
a separated power supply dynamic blood glucose monitoring transmitter comprises a transmitter and a sensor base device; the sensor base device comprises a base and an adhesive tape, and the base is positioned on the adhesive tape; the upper part of the base is provided with an opening, a battery groove and a groove are formed in the base, a battery and a battery cover are arranged in the battery groove, a rotating seat is arranged in the groove, one side of the rotating seat, which is close to the battery groove, is hinged in the groove, a silica gel seat is arranged in the rotating seat, a pair of conductive rubbers is arranged in the silica gel seat, a sensor is arranged to penetrate through the silica gel seat and the rotating seat, the sensor can penetrate through the two conductive rubbers, an opening is formed in one side, close to the battery groove, of the groove, a hole is formed in the adhesive tape, and the sensor can penetrate through the opening and the hole of the adhesive tape; the transmitter comprises a plastic package shell and a circuit board assembly, wherein the plastic package shell is covered on a base, the circuit board assembly is arranged at the inner top of the plastic package shell, and four conductive pins are arranged on the circuit board assembly and can contact the anode and the cathode of the battery and two conductive rubbers.
As a further preferable scheme, the silica gel seat is provided with a first conductive rubber hole and a second conductive rubber hole, and the two conductive rubbers are respectively arranged in the first conductive rubber hole and the second conductive rubber hole; the silica gel seat is internally provided with two square holes, the two conductive rubbers and the two square holes are distributed in a straight line, and the sensor penetrates through the two conductive rubbers.
As a further preferable scheme, a semicircular hole is respectively formed in two sides in the groove, a tough extending rod is respectively arranged on two sides of the end part of the rotating seat, a cylindrical shaft is arranged on the outer side of the extending rod, and the cylindrical shaft is arranged in the semicircular hole to rotate.
As a further preferable scheme, an electrode adapter is respectively arranged on the anode and the cathode of the battery, an electrode connecting piece is arranged on each electrode adapter, two round holes are formed in the battery cover, one round hole corresponds to one electrode connecting piece, and the electrode connecting pieces penetrate through the round holes and are arranged outside the battery cover.
As a further preferable scheme, the four conductive pins on the circuit board assembly are two battery conductive pins and two rubber conductive pins, the two battery conductive pins are respectively connected with an electrode connecting piece, and the two rubber conductive pins are respectively connected with one conductive rubber.
As a further preferable scheme, the end part of the base is provided with a base buckle opening, and the end part of the plastic package shell is provided with an edge boss inserted into the base buckle opening; the side part of the plastic package shell is provided with a shell clamping groove, and the inner side wall of the groove is provided with an elastic buckle clamped into the shell clamping groove.
As a further preferable scheme, a circle of edges of the battery groove is provided with a sealing strip, and a circle of edges of the silica gel seat is provided with a rib.
The system for separating the power supply dynamic blood glucose monitoring transmitter comprises an LC filtering energy storage module, a wireless SOC module, a functional circuit power module, a sensor excitation and conditioning module, an ADC precision enhancement module, a battery and a sensor, wherein the anode and the cathode of the battery are respectively connected with the LC filtering energy storage module through circuits, a connecting wire is arranged between the LC filtering energy storage module and the VDD end of the wireless SOC module, a double-control switch is arranged on the connecting wire and can be connected with the Da end or the functional circuit power module of the wireless SOC module, the functional circuit power module is connected with the sensor excitation and conditioning module through circuits, the Db end of the wireless SOC module is also connected with the sensor excitation and conditioning module through circuits, the wireless SOC module is provided with a built-in ADC precision enhancement module, the ADC precision enhancement module is connected with the sensor excitation and conditioning module through circuits, and the anode and the cathode of the sensor excitation and conditioning module are respectively connected with the sensor through circuits.
The high-precision signal sampling method of the ADC precision enhancement module is characterized by comprising the following steps: injecting a noise voltage with the amplitude of 0 into the sampling signal, and carrying out ADC (analog-to-digital converter) sampling to obtain a Read1 result; step two: injecting an amplitude value into the sampling signal as followsWherein V is ADC_REF Taking the reference voltage of the ADC as d as the target precision bit number, and performing ADC sampling to obtain a Read2 result; step three: the final result read= (read1+read2)/2, and the resulting precision can be enhanced by 1 bit.
Compared with the prior art, the invention has the beneficial effects that: the button cell is separated from the emitter and integrated with the sensor placement. When not in use, the transmitter is not installed on the sensor base, so that the transmitter is in a power-off state, and the button battery does not consume power. When in use, the transmitter is buckled on the sensor base, and the battery on the sensor base is electrically connected with the transmitter to supply power. After the use, the emitter is taken down, and the button cell and the sensor are discarded together. Thus, the button cell only needs to support the sensor for one cycle of power. On one hand, the volume of the button cell can be reduced, and on the other hand, the cost of the cell can be reduced. In addition, the cost is greatly reduced because the transmitter can be reused.
The newly designed ADC precision enhancement circuit can enhance the sampling precision by 1 bit; the LC filter energy storage circuit can reduce the capacity (volume) of a battery on one hand and can make the power supply of a transmitter more stable on the other hand; and the wireless SOC module power supply and the functional circuit power supply are separated to supply power, so that the power consumption is effectively reduced. And a soft power-on method is designed to ensure that the transmitter works more stably and reliably.
Drawings
FIG. 1 is a schematic diagram of the structure of the present invention;
FIG. 2 is an exploded view of a transmitter;
FIG. 3 is an exploded view of a sensor base assembly;
FIG. 4 is a cross-sectional view of a silicone seat;
FIG. 5 is a schematic view of the structure of the base;
FIG. 6 is a schematic view of a battery cover structure;
FIG. 7 is a schematic view of the structure of the rotating base and the silica gel base;
FIG. 8 is a schematic diagram of a system module according to the present invention;
FIG. 9 is a schematic circuit diagram of a functional circuit module;
FIG. 10 is a schematic diagram of a functional circuit power supply soft power-up;
FIG. 11 is a sensor excitation and conditioning module circuit;
FIG. 12 is an ADC precision enhancement module circuit;
FIG. 13 is a circuit of an LC filter tank module;
fig. 14 is a wireless SOC module circuit.
Detailed Description
The following describes in detail the preferred embodiments of the present invention with reference to the accompanying drawings.
As shown in fig. 1, the emitter system is structurally comprised of two parts, an emitter 200 and a sensor mount assembly 300. The sensor electrodes 301 attached to the sensor base unit 300 may be implanted into the recipient tissue by an auxiliary implantation device. The auxiliary implant device can be seen in published patent CN206424078U.
As shown in fig. 2, the hardware of the transmitter 200 includes a circuit board assembly 201 and a plastic package 202. The emitter has a size of 32mm 16mm 5mm, and is convenient to be attached to the skin of a recipient and carried about after being mounted in the sensor base device 300.
The circuit board assembly 201 includes four conductive pins, typically of conductive metal, preferably brass. The conductive pins are led out of the plastic package 202 and are flush with the bottom surface of the plastic package. When the transmitter 200 is snapped into the sensor mount assembly 300, the conductive pins are connected to the sensor S+, S-and the battery V+V-, respectively. The battery 304 in the sensor base 300 supplies power to the transmitter 200, and the transmitter 200 can convert the signal value measured by the sensor 301 into a corresponding physiological parameter and send the physiological parameter to the user receiving end.
The plastic package 202 completely wraps the circuit board assembly (except for 4 conductive pins), so that a waterproof effect can be realized. The left side of the plastic package shell is provided with an edge boss 2021, and two sides of the plastic package shell are respectively provided with a shell clamping groove 2022, when the transmitter is arranged on the sensor base, the edge boss 2021 and the shell clamping groove 2022 can fix the transmitter 200 on the base
As shown in fig. 3, the sensor base assembly 300 basically includes a battery 304 and a sensor 301. Wherein the battery 304 and the transmitter 200 are connected by electrical contacts V + and V-. The sensor 301 and the transmitter 200 are connected by an electrical contact S + S-.
The sensor base device 300 comprises a sensor 301, a base 302, a rubberized fabric 303, a battery 304, a battery adapter 305, an electrode connector 306, a battery cover 307, a waterproof seal 308 of the battery connector, a swivel 309, a silicone base 310, conductive rubber, etc. 311.
The battery adapter 305 may be a metal member such as nickel strap. The battery adapter 305 is connected to the battery 304 and the battery connector 306 by welding or the like.
And the battery 304 is provided with insulating paper outside to prevent the conduction of the anode and the cathode of the battery.
The battery connector 306 is placed on the battery adapter 305 and is compressible by the mounting of the battery cover 307.
The battery connector 306 is resilient and can be in resilient electrical connection with the transmitter. Preferably, the battery connector 306 may be a spring pin with a spring inside that depresses the contact of the battery connector when the transmitter 200 is installed, thereby ensuring reliable contact between the battery connector contact and the transmitter contact.
The surface of the base 302 is provided with a circle of waterproof sealing ring 308, and the waterproof sealing ring can be made of elastic materials such as silica gel, TPE, TPU and the like. The waterproof sealing ring can be directly injection molded on the base, and also can be bonded on the base through later stage. The waterproof sealing ring is trapezoidal or triangular, so that the emitter can be well arranged, and the waterproof sealing ring can be well waterproof. When combined with the bottom plane of the emitter, the waterproof effect can be achieved, and the waterproof grade can reach IPX7.
In the unused state, the transmitter 200 is not yet mounted on the sensor mount device 300, and therefore, the transmitter 200 is in the power-off state, and the battery 304 is not consumed. When in use, the transmitter 200 is snapped onto the sensor mount 300, and the battery on the sensor mount 300 provides power to the transmitter 200 through an electrical connection. When used, the transmitter is removed and the battery 304 is discarded along with the sensor.
As shown in fig. 4, the sensor 301 is implanted in subcutaneous tissue of an organism for sensing a primary signal of an analyte. Sensor 301 includes at least 1 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 lead 2011 and the rubber lead 2012 of the emitter 200, respectively.
The base 302 is fixed to the skin of the subject by a non-woven fabric adhesive tape 303, and is fixedly connected to the transmitter 200.
As shown in fig. 5, the base 302 has a battery compartment 3021 of 12mm in the middle for receiving the battery 304. The positive and negative electrodes of the battery are connected to the battery connector 306 by the battery adapter 305 and then led to the outer surface of the base by the battery connector.
The base 302 is provided with a base snap opening 3023 at the end. The top of the opening is a plane, and the bottom of the opening is provided with an inclined plane with a certain angle. The top surface is adapted to mate with the edge boss 2021 of the emitter 200 to limit the emitter. The bottom bevel facilitates emitter installation.
The base 302 has a recess 3024 in the right portion for receiving the swivel 309. When the sensor 301 is implanted, the rotating seat rotates clockwise by a certain angle and finally is attached to the bottom surface of the groove. The recess 3024 has an opening 3025 in the lower left side through which the sensor 301 can pass.
Two sides of the groove 3024 are provided with a semicircular hole 3026, which cooperates with the cylindrical shaft 3092 of the swivel 309 so that the swivel can rotate along the axis of the hole.
A bevel is provided above the semicircle orifice 3026, which is snapped into the semicircle orifice for facilitating the rotation of the seat cylinder shaft.
The elastic buckles 3027 are arranged on two sides of the base 302 and are used for being matched with the housing clamping grooves 2022 on two sides of the emitter, when the emitter is installed, the elastic buckles on two sides of the base are outwards opened, and after the emitter is installed in place, the elastic buckles retract. The bottom surface of the elastic buckle is blocked with the clamping groove of the emitter to limit the movement of the emitter.
As shown in fig. 6, a battery cover 307 is provided to cooperate with the base 302 to secure the battery connector 306 and the battery 304. A battery cover recess 3071 is provided in the middle of the battery cover 307 for accommodating the battery 304. The battery connector is fixed by the cooperation of 2 cylindrical steps 3022 corresponding to the bottom surface of the base, wherein the two ends of the battery connector are respectively provided with a cylindrical hole step surface 3072. The 2 circular holes 3073 in the top of the battery cover 307 allow the elastic members of the battery connector to pass through so as to contact the emitter contacts.
As shown in fig. 7, the swivel base 309, on the one hand, provides support for the silicone base 310 thereon in the uninstalled state; on the other hand, when the installation is completed, it can be rotated around the base to the installed state.
Two sides of the rotating seat 309 are provided with 2 extending rods 3091 which have certain elasticity and can retract inwards when being stressed; after the applied force is removed, the extension rod can be restored to the original position.
The end of the rod is provided with 1 cylindrical shaft 3092 which is matched with the semicircular hole of the base.
The cylindrical shaft 3092 has a bevel on its side which contacts and guides the bevel of the base when the rotating base is mounted in the base. Under the action of the extrusion force, the extending rod 3091 is contracted inwards, the cylindrical shaft is clamped into the semicircular hole of the base, and the extending rod can be restored to the original position. The freedom of the rotating seat and the base part is limited, and the rotating seat can only rotate around the cylindrical axis.
The silica gel seat 310 is used for storing conductive rubber 311, providing deformation space for the conductive rubber and limiting the conductive rubber; on the other hand, after the silica gel seat is combined with the plane of the emitter, the waterproof effect can be achieved, and the waterproof grade can reach IPX7.
The silica gel base 310 has a first conductive rubber hole 3101 and a second conductive rubber hole 3102 in the middle. The circular hole is used for placing the conductive rubber 311.
The number of the conductive rubbers 311 is 2, after implantation, the sensor 301 passes through the conductive rubbers, and each conductive rubber is respectively connected with the electrical contacts S+ and S-of the sensor 301 and the emitter 200, so that elastic electrical connection between the sensor and the emitter is realized. The conductive rubber maintains the position of the sensor by friction under pressure except when the circuit is connected.
The silica gel base 310 also has 2 square holes 3103. The square hole aims to reduce the resistance when the guide needle and the puncture needle are removed from the silica gel seat.
The silica gel base 310 has a ring of trapezoidal or triangular ribs 3104 on the top, which can make the emitter more convenient to install and waterproof.
Before use, the rotating seat 309 is arranged at 45 ° with respect to the base 302, and a hollow guide needle in the implanter passes through the rotating seat 309 and the silicone seat 310 in parallel and through the first conductive rubber hole 3101 and the second conductive rubber hole 3102; a hollow lancet is positioned within the guide needle with a tip for puncturing the skin of the subject and the sensor 301 is a solid needle of flexible material positioned within the lancet. In use, the sensor 301 is carried by the needle through the driving force of the implanter, the needle and guide needle are withdrawn, the sensor 301 is retained in the body, and the implanter is removed and the emitter 200 is mounted on the base 302. At this time, the battery on the base supplies power to the transmitter through the battery lead 2011 connected to v+v-. The rubber lead 2012 connected to the emitter S + S-, the conductive rubber 311, and the sensor 301 form an electrical circuit. When glucose oxidase on the sensor reacts with glucose inside the receptor, a weak current is generated. The transmitter can measure the current value through the electric loop. And converts the measured current value into a blood glucose value of the subject by an algorithm internal to the transmitter. The blood glucose values are then transmitted to the corresponding display device via the wireless transmission module.
As shown in fig. 8, in the SOC module, VDD is the power supply voltage of the SOC, and Da, db, dc are the digital output pins of the SOC module. The Da pin is used for controlling the switch S1 to be opened and closed, so that whether the battery supplies power to the functional circuit power supply module or not is controlled. Db is used to select the level of the sensor excitation circuitry, which allows the sensor excitation module to provide both high and low excitation voltage signals to the sensor. Dc is used to inject a noise signal into the ADC accuracy enhancement module. Ain1 and Ain2 are ADC inputs for sampling the conditioned and noise injected sensor voltage output by the ADC precision enhancement module.
As shown in fig. 9, Q2 (corresponding to switch S1 of fig. 1) implements the switch S1 module function. The gate vper_shdn (corresponding to Da signal of fig. 1) is connected to Pin37 of bluetooth master control chip U0 in the wireless SOC module circuit.
When VPER SHDN is low, VBAT and v_per are on. The battery starts to supply power to the functional circuits including the sensor excitation and conditioning module circuit and the ADC precision enhancement module circuit.
When VPER_SHDN is at high level, VBAT and V_PER are disconnected, and the functional circuit comprises a sensor excitation and conditioning module circuit and an ADC precision enhancing module circuit which do not work, so that power consumption can be saved. The L1 and L2 inductors are mainly used for dividing the digital circuit and the analog circuit, and the analog circuit signals belong to micro signal sampling, so that the analog signals can be ensured to be cleaner by dividing the digital and analog circuits. U1 is a precision reference power supply, with a precision of one thousandth, input is an analog power supply VCCA, output is a reference voltage signal vs_ref, and vs_ref is used as a reference level for applying sensor excitation. C1 and C2 are power supply filter capacitors.
The invention adopts soft power-on of the power supply of the functional circuit, when the functional circuit needs power-on, the wireless SOC module applies a PWM chopping waveform with a timing length t to the gate electrode of the Q2, as shown in figure 10, the PWM duty ratio gradually increases, at the moment, the output voltage of the analog switch slowly rises, the current maintains a smaller value range during the voltage rising period, and the current magnitude is related to the PWM period and the duty ratio. The power-on current in a PWM soft power-on mode can be adjusted according to the PWM duration, the duty ratio and the PWM period, so that the method is used. If soft power-on is not adopted, a high-leveling and hard-on mode is directly adopted for the gate electrode of the Q2, and a large number of filter capacitors are arranged in the functional circuit, the instant charging current (also in a pulse current mode) tends to be quite large at the moment, and the capacity in the LC filter capacitors is possibly insufficient, so that the voltage of a battery is lowered, and the system is subjected to the power-failure reset phenomenon.
As shown in fig. 11, R1, R2, R3, R4, R5, R6, Q1, and U5 form a sensor excitation circuit, and the gate of Q1 is connected to Pin39 of the bluetooth master control chip U0 in the wireless soc module. The sensor excitation circuit output vs+ is connected to the sensor anode via the emitter electrical contact s+. VS_REF is functional circuit power module is provided. The calculated relationship of the outputs VS + and VS REF is as follows,
vs_sel (corresponding to the Db signal of fig. 1) is high:
wherein R4// R5 represents R4, R5 parallel equivalent resistance value
Vs_sel (corresponding to Db signal of fig. 1) is low:
r7, R8, C5, U6 form a conditioning circuit, which is essentially an I-V operation circuit, and functions 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 sensor cathode through emitter electrical contact S-and according to the operational amplifier analysis method, the voltage of S-should be equal to VS_REF. C3 and C39 are U5, U6 power decoupling capacitors. C8 is a filter capacitor that controls the noise bandwidth of the current signal.
Let the sensor current flowing into S-be I 0 ADC_GLU and input I 0 Relation of (2) the method comprises the following steps:
ADC_GLU＝VS_REF+I 0 *R 8
since the sampled current is in the microampere range, R8 is preferably 1MΩ.
The accuracy of an analog-to-digital conversion circuit ADC built in a general main control chip is fixed and limited, and sometimes the application requirements cannot be met. The usual solution is to use an off-chip ADC chip, but off-chip ADCs are often expensive. Therefore, the ADC precision enhancement circuit module is invented, and the ADC precision enhancement circuit adopts a noise injection method, so that the sampling precision is enhanced by 1 bit again on the basis of the fixed precision of the built-in ADC of the main control chip of the wireless SOC module. The sampling method comprises the following steps: firstly, injecting a noise voltage with the amplitude of 0 into a sampling signal, and carrying out ADC (analog-to-digital converter) sampling to obtain a Read1 result; step2, injecting an amplitude value into the sampling signalNoise voltage (V) ADC_REF Taking the ADC reference voltage, d is the target precision bit number), and carrying out ADC sampling, wherein the result is Read2; step3, the final result read= (read1+read2)/2, and the obtained result precision can be enhanced by 1 bit.
As shown in fig. 12, two-stage noise signals are injected on the sampled signals to sample respectively, and after sampling and averaging, the accuracy can be increased by 1-bit resolution.
The circuit for injecting noise signals is realized by an addition operation circuit, and each path of sampling needs one addition operation circuit. As shown in the figure, U8, R13, R14, R15, R16 constitute a precision enhancing circuit for vs_ref. U9, R17, R18, R19, R20 form an accuracy enhancement circuit for the ADC_GLU. The structure of each path of ADC precision enhancing circuit is the same. The accuracy enhancing circuit outputs ADC_R and ADC_G after being filtered by a post-stage filter circuit formed by R9R10C8C9C10, and the post-stage filter circuit is connected to built-in ADC pins Pin41 and Pin42 of a Bluetooth main control chip U0 in the wireless SOC module for analog-to-digital conversion. Bit11 (corresponding to the Dc signal of fig. 1) is a noise injection signal, connected to Pin38 of U0. The injected signal is only Gao Dingping V or low 0V.
Taking the VS_REF path as an example, let R 13 ＝k*R 14 ，R 19 ＝k*R 20 Therefore, it isWhere k=2 d . When the actual precision of the ADC is 10 bits and the target precision is 11 bits, k should take a near value of 2048.
Step1: bit11 outputs low level, V Bit11 =0, ADC sampling, resulting in Read1;
step2: bit11 outputs high level, V Bit11 =3, ADC sampling, resulting in Read2;
step3: the final result read= (read1+read2)/2 is the result after enhancing the precision.
In this example, the standard conversion accuracy of the ADC of the Bluetooth main control chip is 10 bits when no oversampling occurs, and the reference voltage is calculated according to 1 (100%), and the accuracy is thatThe result register is set as a 12-bit register, and the high order of the result is aligned with the result register. Table 1 table 2 shows the calculation process with enhanced accuracy after signal injection.
Table 1.10 bit ADC and 11 bit ADC encoding table
Table 2 adc accuracy enhancement signal calculation example table
From table 2, it is known that by injecting (superimposing) a noise signal on a sampled voltage signal in a method, summing up the sampling results of each injected noise signal, and then averaging the results, the 1-bit sampling accuracy can be increased.
As shown in fig. 13, the LC filter tank circuit may select a button battery with smaller capacity (volume), so as to effectively reduce the influence of the pulse current of the wireless SOC module on the battery voltage when the radio frequency event occurs, so that the power supply of the transmitter is more stable, and correspondingly, the battery with smaller capacity (volume) may be selected, so that the influence of the pulse current of the wireless SOC module on the battery voltage when the radio frequency event occurs is effectively reduced, so that the power supply of the transmitter is more stable, and correspondingly, the battery with smaller capacity (volume) may be selected;
in the LC filter energy storage circuit, V+V-is connected with the anode and the cathode of a battery, and VDD_NRF supplies power for a Bluetooth main control chip in the wireless SOC module.
L6, C34, C35, C36, C37 constitute LC filter tank circuits. Because the discharging capacity and capacity of the battery are related, the pulse discharging capacity of a conventional small-capacity CR series button battery is about 5mA, and when a radio frequency event occurs (when data is wirelessly transmitted or received), the current load of the Bluetooth chip is as high as 12mA or more, which is far more than the pulse discharging capacity of the battery.
When the pulse discharging capacity of the battery is insufficient, the voltage at two ends of the battery is pulled down, and when the voltage is too low, the Bluetooth main control chip is reset, so that the whole system fails. On the other hand, repeated pulsed currents may cause damage to the battery itself, i.e. the pulsed current may cause the actual operating capacity of the battery to be much smaller than the nominal capacity.
Considering that the radio frequency event is intermittent, the inductance-capacitance filtering energy storage circuit is added in the embodiment, when no pulse current occurs, the C34, C35, C36 and C37 mainly serve as energy storage, when no radio frequency time occurs, the whole circuit has small power consumption, so that the capacitance charge of a battery is larger than the capacitance discharge of a system circuit, and redundant energy is stored in the capacitance. When a radio frequency event occurs, the pulse current required by the system circuit is preferentially obtained from the capacitor, so that the battery does not need to provide the pulse current, and therefore, the battery is in a more gentle discharge state in the whole working period, the voltage drop event is effectively restrained, and the damage of the pulse current to the battery is prevented.
The inductor L6 is mainly used for suppressing the current amplitude of the capacitor charged by the battery, because the pulse current is a high-frequency characteristic current, and the inductor L6 can exhibit a large impedance characteristic for high frequencies. When a pulsed current occurs, L6 may prioritize battery discharge over battery discharge, i.e., use the amount of power stored in the capacitor.
As shown in fig. 14, in the wireless SOC module circuit, the bluetooth chip U0 is preferably used as the main control chip.
The wireless SOC module power supply and the functional circuit power supply are separated and independently supply power. The functional circuit power supply mainly supplies power for the sensor excitation and conditioning circuit and the precision enhancing circuit. The method of separately supplying power is adopted, and the principle of supplying power is adopted according to who works and who supplies power. When the functional circuit does not need to work, the battery power can be not consumed, and the power consumption is effectively reduced. In order to reliably electrify the functional circuit, a soft electrifying method is designed, so that the pulse current amplitude at the electrifying moment is effectively restrained, and the transmitter works more reliably.
The capacitors C27, C28 and the crystal Y1 provide a high-frequency clock source for the Bluetooth chip, and the crystal Y1 is preferably 16MHz. The capacitors C21, C22 and the crystal Y2 provide a low frequency clock source for the Bluetooth chip, and the crystal Y2 is preferably 32.768kHz.
DV, DIO, DCK, DG is a simulation port for simulating and programming programs. C23, C24, C25, C26, C29, C30 and C33 are Bluetooth chip power decoupling capacitors. L4, C31 and antenna ANT1 constitute a Bluetooth radio frequency circuit for modulating wireless signals.
Pin37 of U0 is connected to the gate of switch S1 circuit Q2 for controlling the on-off of the power supply of the functional circuit. When the functional circuit is not required to work, a low level is output, and the functional circuit is in a non-working state at the moment, so that the purpose of saving power consumption is achieved.
Pin41 and Pin42 of U0 are sensor current sampling signals passing through the ADC precision enhancement module circuit and are used for calculating the blood glucose concentration.
Pin6 of U0 is connected to the positive electrode of the battery, and the voltage value of the battery is collected and used for calculating the electric quantity of the battery according to the voltage-electric quantity curve of the battery.
Pin39 of U0 is connected to the gate of Q1 in the sensor excitation and conditioning module circuit for selecting the level at which the sensor applies excitation, in this example by a mosfet, two levels of excitation can be applied to the sensor.
While the foregoing is directed to embodiments of the present invention, other and further details of the invention may be had by the present invention, it should be understood that the foregoing description is merely illustrative of the present invention and that no limitations are intended to the scope of the invention, except insofar as modifications, equivalents, improvements or modifications are within the spirit and principles of the invention.

Claims (1)

1. The system for randomly separating power supply dynamic blood glucose monitoring transmitters is characterized in that: comprises an LC filtering energy storage module, a wireless SOC module, a functional circuit power module, a sensor excitation and conditioning module, an AD C precision enhancement module, a battery and a sensor,
the positive electrode and the negative electrode of the battery are respectively connected with an LC filtering energy storage module through a circuit, a connecting wire is arranged between the LC filtering energy storage module and the VDD end of the wireless SOC module to supply power to the SOC, a double-control switch is arranged on the connecting wire, and the double-control switch can be connected with the D a end of the wireless SOC module or a functional circuit power supply module;
the power supply module circuit of the functional circuit is connected with the sensor excitation and conditioning module, the Db end of the wireless SOC module is also connected with the sensor excitation and conditioning module circuit, and the Db end is used for selecting the level of the sensor excitation circuit, so that the sensor excitation module can provide two excitation voltage signals of high level and low level for the sensor;
when the Da end signal is in a low level, the double-control switch is communicated with the power module of the functional circuit, and the battery starts to supply power to the functional circuit, wherein the functional circuit comprises a sensor excitation and conditioning module circuit and an ADC precision enhancing module circuit; the wireless SOC module applies a PWM chopping waveform with a fixed duration t to the double-control switch when the functional circuit needs to be powered on, the PWM duty ratio is gradually increased, and the current magnitude is related to the PWM period and the duty ratio; the power-on current in a PWM soft power-on mode is adjusted according to the PWM duration, the duty ratio and the PWM period;
when the Da end signal is in a high level, the double-control switch is disconnected with the power module of the functional circuit, and the functional circuit comprises a sensor excitation and conditioning module circuit and an ADC precision enhancement module circuit which do not work, so that the power consumption can be saved;
the gate electrode in the sensor excitation and conditioning module is connected to a Bluetooth main control chip in the wireless SOC module, and the output VS+ of the sensor excitation circuit is connected with the positive electrode of the sensor through the electric contact S+ of the transmitter; VS_REF is the precise reference voltage source output in the functional circuit power supply module; the calculated relationship of the outputs vs+ and vs_ref is as follows:
vs_sel is high:
wherein R4// R5 represents R4 and R5 are parallel equivalent resistance values;
vs_sel is low:
let the sensor current flowing into S-be I 0 ADC_GLU and input I 0 The relation of (2) is:
ADC_GLU＝VS_REF+I 0 *R 8
since the sampled current is at microampere level, R8 is 1MΩ;
wherein R1, R2, R3, R4, R5, R6, Q1 and U5 form a sensor excitation circuit, and the gate electrode of the Q1 is connected to Pin39 of the Bluetooth master control chip U0 in the wireless soc module; the output VS+ of the sensor excitation circuit is connected with the anode of the sensor through the electrical contact S+ of the transmitter; VS_REF is the precise reference voltage source output in the functional circuit power supply module; r7, R8, C5 and U6 form a conditioning circuit; pin3 of U6 is connected to the sensor cathode through emitter electrical contact S-; c3 and C39 are U5, U6 power decoupling capacitors; c8 is a filter capacitor, and the noise bandwidth of the circulating current signal is controlled;
the wireless SOC module is provided with an internal ADC module, a Dc end of the wireless SOC module and the internal ADC module are both connected with the ADC precision enhancement module, the Dc end is used for injecting noise signals into the ADC precision enhancement module, the ADC precision enhancement module is connected with the sensor excitation and conditioning module through a circuit, and the anode and the cathode of the sensor excitation and conditioning module are respectively connected with the sensor through a circuit;
the built-in ADC module is internally provided with an Ain1 end and an Ain2 end and is used for sampling the sensor voltage which is output by the ADC precision enhancement module and is subjected to conditioning and noise injection.
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