CN210056040U - Separate power supply dynamic blood sugar monitoring transmitter and system thereof - Google Patents
Separate power supply dynamic blood sugar monitoring transmitter and system thereof Download PDFInfo
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- CN210056040U CN210056040U CN201920621728.4U CN201920621728U CN210056040U CN 210056040 U CN210056040 U CN 210056040U CN 201920621728 U CN201920621728 U CN 201920621728U CN 210056040 U CN210056040 U CN 210056040U
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Abstract
The utility model discloses a dynamic blood sugar monitoring transmitter with separated power supply and a system thereof, which structurally comprises a transmitter and a sensor base device; the sensor base device is divided into a base and an adhesive tape, a battery jar and a groove are arranged in the base, a battery is arranged in the battery jar, a rotating seat is arranged 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 rubber is arranged in the silica gel seat, the transmitter comprises a circuit board assembly, four conductive needles are arranged on the circuit board assembly, and the positive electrode and the negative electrode of the battery can be contacted and the two conductive rubbers can be contacted. Compared with the prior art, the utility model discloses can separate button cell from the transmitter, be in the same place with the sensor integration, when not using, on the sensor base was not packed into to the transmitter yet, consequently, the transmitter was in the outage state, and button cell is also not power consumptive, and during the use, on the sensor base was buckled into to the transmitter, battery on the sensor base passed through electrical connection and supplied power for the transmitter.
Description
Technical Field
The utility model relates to a separation power supply developments blood sugar monitoring transmitter and system thereof belongs to wearable medical instrument technical field.
Background
The traditional dynamic blood sugar emitter mainly comprises three parts, namely a button cell, a circuit board and a plastic package shell. Due to 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 subjected to integrated plastic package molding, so that the emitter battery cannot be replaced, the service time of the disposable sensor is generally unequal within 3-14 days, the disposable sensor is discarded after the use, and the emitter is basically unusable after the service life of the battery is finished. From the cost perspective, the cost of the transmitter plastic package shell and the circuit board is far larger than the cost of the battery, and the service life of the transmitter plastic package shell and the service life of the circuit board are also far larger than the service life of the battery. Therefore, the circuit board and the plastic package shell can be greatly wasted, and material cost and waste are increased.
The problem of cost waste can be solved by adopting the polymer rechargeable lithium battery, but the polymer battery has the problem of loss, and the service life of the polymer battery is still far shorter than that of a circuit board and a plastic package shell after the charging frequency is considered, so that the problem cannot be fundamentally solved. In addition, the polymer rechargeable battery is not suitable for the standard product of the transmitter, and usually requires a battery supplier to supply the product in a non-standard manner, which increases the purchasing difficulty.
In addition, in order to effectively utilize the service life of the circuit board and the plastic package shell of the emitter, the cost is reduced and the waste is reduced. Button cells with a slightly larger volume (larger electric quantity) are usually selected, so that the transmitter cannot be designed to be smaller, and the 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 life of the battery, on one hand, the battery with a smaller volume can be selected, the system volume is reduced, and the wearing experience is improved.
In addition, the dynamic blood glucose emitter calculates the blood glucose concentration by sampling the current value of the sensor, so the accuracy of the sampled sensor directly influences the accuracy of the calculated blood glucose concentration, and the wireless SOC module generally has a built-in ADC sampling circuit, the accuracy of the circuit is generally about 10-12 bits, and the effective accuracy may be slightly lower than the nominal value. If higher accuracy is required, expensive external ADC circuitry is added.
SUMMERY OF THE UTILITY MODEL
The utility model discloses the technical problem that needs to solve is not enough to above-mentioned prior art, and provides the high accuracy developments blood sugar monitoring transmitter of a separation power supply and system thereof.
In order to solve the technical problem, the utility model discloses a technical scheme is:
a separate power supply dynamic blood sugar 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 sensor comprises a base, a rotating seat, a pair of conductive rubbers, a sensor and a sensor, wherein the upper part of the base is provided with an opening, a battery jar and a groove are arranged in the base, a battery and a battery cover are arranged in the battery jar, the rotating seat is arranged in the groove, one side, close to the battery jar, of the rotating seat is hinged in the groove, a silica gel seat is arranged in the rotating seat, the silica gel seat is internally provided with the pair of conductive rubbers, the sensor penetrates through the silica gel seat and the rotating seat, the sensor can penetrate through the two conductive rubbers, one side, close to the battery jar, of the; the transmitter comprises a plastic package shell and a circuit board assembly, the plastic package shell covers the base, the circuit board assembly is installed at the top in the plastic package shell, and the circuit board assembly is provided with four conductive pins which can contact the positive electrode and the negative electrode of the battery and two conductive rubbers.
As a further preferred scheme, a first conductive rubber hole and a second conductive rubber hole are formed in the silicon base, and the two conductive rubbers are respectively installed in the first conductive rubber hole and the second conductive rubber hole; two square holes are further formed in the silicon rubber seat, the two conductive rubbers and the two square holes are linearly distributed, and the sensor penetrates through the two conductive rubbers.
As a further preferable scheme, two sides in the groove are respectively provided with a semicircular hole, two sides of the end part of the rotating seat are respectively provided with a flexible extension bar, the outer side of the extension bar is provided with a cylindrical shaft, and the cylindrical shaft is arranged in the semicircular hole to rotate.
As a further preferable scheme, the positive electrode and the negative electrode of the battery are respectively provided with an electrode adapter, each electrode adapter is provided with an electrode connecting piece, the battery cover is provided with two round holes, one round hole corresponds to one electrode connecting piece, and the electrode connecting pieces penetrate through the round hole parts and are arranged outside the battery cover.
As a further preferred scheme, 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 with one electrode connecting piece, and the two rubber guide pins are respectively connected with one conductive rubber.
As a further preferred scheme, the end of the base is provided with a base buckle opening, and the end 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 which is clamped into the shell clamping groove.
As a further preferred scheme, one circle of the edge of the battery jar is provided with a sealing strip, and one circle of the edge of the silica gel seat is provided with a rib position.
The system of the separated power supply dynamic blood sugar monitoring emitter comprises an LC filtering energy storage module, a wireless SOC module, a functional circuit power supply module, a sensor excitation and conditioning module, an ADC precision enhancing 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 lines, a connecting line 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 line and can be connected with the Da end of the wireless SOC module or the functional circuit power supply module, the functional circuit power supply module is connected with the sensor excitation and conditioning module through a line, the Db end of the wireless SOC module is also connected with the sensor excitation and conditioning module through a line, the wireless SOC module is provided with a built-in ADC module, the Dc end of the wireless SOC module and the built-in ADC module are both connected with the ADC precision enhancing module, and the ADC precision, the positive electrode and the negative electrode of the sensor excitation and conditioning module are respectively connected with the sensor through lines.
Compared with the prior art, the beneficial effects of the utility model are that: the button cell is separated from the emitter and is integrated with the sensor. When the button type transmitter is not used, 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 the sensor is used, the emitter is buckled on the sensor base, and the battery on the sensor base supplies power to the emitter through electrical connection. When the transmitter is taken down after the use, the button cell and the sensor are discarded together. Thus, the button cell only needs to support the power of the sensor for one period. 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 transmitter can be reused, so that the cost is greatly reduced.
The newly designed ADC precision enhancing circuit can enhance the sampling precision by 1 bit; the LC filtering energy storage circuit can reduce the battery capacity (volume) on one hand and can ensure that the power supply of the emitter is more stable on the other hand; and the wireless SOC module power supply and the functional circuit power supply are in a separated power supply mode, 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 structural view of the present invention;
FIG. 2 is an exploded view of the transmitter;
FIG. 3 is an exploded view of a sensor mount apparatus;
FIG. 4 is a cross-sectional view of a silicone mount;
FIG. 5 is a schematic structural view of a base;
FIG. 6 is a schematic view of a battery cover structure;
FIG. 7 is a schematic structural view of a rotary seat and a silica gel seat;
fig. 8 is a schematic diagram of a system module according to the present invention;
FIG. 9 is a 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 an LC filter tank circuit;
fig. 14 is a wireless SOC module circuit.
Detailed Description
The preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.
As shown in fig. 1, the transmitter system is structurally composed of two parts, a transmitter 200 and a sensor base unit 300. Sensor electrodes 301 attached to sensor mount apparatus 300 may be implanted into the recipient tissue via an auxiliary implant device. Supplementary implant devices can be found in the published patent CN 206424078U.
As shown in fig. 2, the transmitter 200, the hardware of which includes a circuit board assembly 201 and a plastic casing 202. The emitter is about 32mm 16mm 5mm in size, and after being arranged in the sensor base device 300, the emitter is convenient to be attached to the skin of a receptor and carried about.
The circuit board assembly 201 includes four conductive pins, and the conductive pins are generally made of conductive metal, preferably brass. The conductive pins are led out from the plastic package shell 202 and are flush with the bottom surface of the plastic package shell. When the transmitter 200 is snapped into the sensor base unit 300, the conductive pins are connected to the sensors S +, S-and the battery V + V-, respectively. The transmitter 200 is powered by the battery 304 in the sensor base 300, and the transmitter 200 can convert the signal value measured by the sensor 301 into a corresponding physiological parameter, and transmit the physiological parameter to the receiving end of the user.
The plastic package shell 202 completely wraps the circuit board assembly (except for 4 conductive pins), and can achieve a waterproof effect. The plastic package casing has edge boss 2021 on the left side and casing clamping grooves 2022 on the two sides, and when the emitter is mounted on the sensor base, the emitter 200 can be fixed on the base by the edge boss 2021 and the casing clamping grooves 2022
As shown in fig. 3, the sensor base unit 300 mainly includes a battery 304 and a sensor 301. Wherein the battery 304 and the transmitter 200 are connected by electrical contacts V + and V-. Sensor 301 and transmitter 200 are connected by electrical contact S + S-.
The sensor base device 300 comprises a sensor 301, a base 302, an adhesive tape 303, a battery 304, a battery adaptor 305, an electrode connector 306, a battery cover 307, a waterproof sealing ring 308 of the battery connector, a rotating base 309, a silica gel base 310, conductive rubber and the like 311.
The battery adapter 305 may be a metal component such as a nickel strap. The battery adapter 305 is connected to the battery 304 and the battery connector 306 by welding or the like.
The battery 304, the battery outside is equipped with insulating paper, prevents that battery positive negative pole from switching on.
The battery connector 306 is placed on the battery adapter 305 and is pressed by the battery cover 307.
The battery connector 306 is resilient and is in resilient electrical communication with the transmitter. Preferably, the battery connector 306 may be a pogo pin with a spring inside to press down the battery connector contacts when the transmitter 200 is loaded, thereby ensuring reliable contact between the battery connector contacts and the transmitter contacts.
The surface of the base 302 is provided with a circle of waterproof sealing ring 308 which can be made of elastic materials such as silica gel, TPE (thermoplastic elastomer), TPU (thermoplastic polyurethane) and the like. The waterproof sealing ring can be directly injected 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 better arranged, and the waterproof effect can be better achieved. When the waterproof coating is combined with the bottom plane of the emitter, the waterproof effect can be achieved, and the waterproof grade can reach IPX 7.
In the non-use state, the transmitter 200 is not yet installed in the sensor mount apparatus 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 snaps onto the sensor base unit 300 and a battery on the sensor base unit 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, a sensor 301 is implanted in the subcutaneous tissue of a living being for sensing a raw 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 guide pin 2011 and the rubber guide pin 2012 of the transmitter 200, respectively.
The base 302 is fixed to the skin of the recipient by a non-woven fabric tape 303, and is fixedly connected to the transmitter 200.
As shown in FIG. 5, the base 302 has a battery container 3021 with a diameter of 12mm in the middle for accommodating the battery 304. The positive and negative poles of the battery are connected to the battery connector 306 through the battery adapter 305, and then led to the outer surface of the base through the battery connector.
The base 302 has 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 used for matching with the edge boss 2021 of the emitter 200 to limit the emitter. The bottom inclined plane is convenient for the installation of the emitter.
The base 302 has a recess 3024 in the right portion thereof for receiving the rotary base 309. After the sensor 301 is implanted, the rotating base rotates clockwise by a certain angle and finally fits with the bottom surface of the groove. The recess 3024 has an opening 3025 on the lower left side through which the sensor 301 can pass.
A semicircular hole 3026 is formed on each side of the recess 3024, and the semicircular hole is engaged with the cylindrical shaft 3092 of the rotary base 309 so that the rotary base can rotate along the axis of the hole.
An inclined plane is arranged above the semicircular hole 3026, and the inclined plane is clamped into the semicircular hole for facilitating the cylindrical shaft of the rotating seat.
As shown in fig. 6, a battery cover 307 is used to cooperate with the base 302 to secure the battery connector 306 and the battery 304. A battery cover groove 3071 is provided in the middle of the battery cover 307 for accommodating the battery 304. Two ends of the battery connector are respectively provided with a cylindrical hole step face 3072, and the battery connector is fixed by matching with 2 cylindrical steps 3022 corresponding to the bottom surface of the base. The top 2 of the battery cover 307 has circular holes 3073 to allow the resilient members of the battery connector to pass through and make contact with the transmitter contacts.
As shown in fig. 7, the rotary 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 about the base to the installed state.
Two sides of the rotary seat 309 are provided with 2 extension bars 3091, and the extension bars have certain elasticity and can contract inwards when stressed; after the application of force is cancelled, the extension bar can be restored to the original position.
The end parts of the out-rods are respectively provided with 1 cylindrical shaft 3092 which is matched with the semicircular hole of the base.
The cylindrical shaft 3092 has a slope on its side surface, and when the rotary seat is installed in the base, the slope of the cylindrical shaft contacts and guides the slope of the base. Under the action of extrusion force, the extension bar 3091 contracts inwards, the cylindrical shaft is clamped in the semicircular hole of the base, and the extension bar can be restored to the original position. The degree of freedom of the rotary seat and the base part is limited at the moment, and the rotary seat can only rotate around the cylindrical axis.
The silicone base 310 is used for storing the conductive rubber 311, providing a 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 IPX 7.
The silicone seat 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 the implantation is completed, the sensor 301 penetrates through the conductive rubbers, and each conductive rubber is respectively connected with the electrical contacts S +, S-of the sensor 301 and the emitter 200, so that the elastic electrical connection between the sensor and the emitter is realized. The conductive rubber keeps the position of the sensor under the action of pressure through friction except for the circuit connection effect.
The silica gel base 310 is also provided with 2 square holes 3103. The square hole is used for reducing resistance when the guide needle and the puncture needle withdraw from the silica gel seat.
The top of the silica gel base 310 is provided with a circle of trapezoidal or triangular rib 3104, which can make the emitter more portable and waterproof.
Before use, the rotating base 309 and the base 302 are arranged at 45 degrees, and a hollow guide needle in the implanter passes through the rotating base 309 and the silica gel base 310 in parallel and passes through a first conductive rubber hole 3101 and a second conductive rubber hole 3102; the hollow puncture needle is positioned in the guide needle, the needle point of the hollow puncture needle is used for puncturing the skin of a receptor, and the sensor 301 is a solid needle body made of soft materials and positioned in the puncture needle. When the injector is used, the puncture needle with the sensor 301 enters a human body through the driving force of the injector, then the puncture needle and the guide needle can be drawn out, the sensor 301 is kept in the human body, finally, the injector is disassembled, and the emitter 200 is arranged on the base 302. At this point, 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 transmitter 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 the measured current value is converted into the blood sugar value of the receptor through an internal algorithm of the emitter. And then the blood glucose value is transmitted to the corresponding display equipment through the wireless transmission module.
As shown in fig. 8, in the SOC module, VDD is the supply voltage of SOC, and Da, Db, and Dc are SOC module digital output pins. The Da pin is used for controlling the opening and closing of the switch S1, so as to control whether the battery supplies power to the functional circuit power supply module. Db is used to select the level of the sensor excitation circuitry, which causes 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 precision 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. Its gate VPER _ SHDN (corresponding to the Da signal of fig. 1) is connected to Pin37 of the 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 circuit comprising 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 comprising the sensor excitation and conditioning module circuit and the ADC precision enhancement module circuit does not work, so that the power consumption can be saved. The L1 and L2 inductors are mainly used for dividing digital circuits and analog circuits, and because analog circuit signals belong to tiny signal sampling, the division of the digital circuits and the analog circuits can ensure that the analog signals are cleaner. 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 utility model discloses a to the soft electricity that goes up of functional circuit power, when the functional circuit need go up the electric work, the PWM chopping waveform of a fixed time length t is applyed to the Q2 gate pole to wireless SOC module, like figure 10, the PWM duty cycle crescent, analog switch's output voltage is slowly rising this moment, and its electric current can maintain a less value scope during voltage rising, and electric current size and PWM cycle and duty cycle have the relation. The power-on current adopting the PWM soft power-on mode can be adjusted according to the PWM duration, the duty ratio and the PWM period, so the method is adopted. If the mode of high leveling and hard opening is directly adopted for the gate of the Q2 instead of soft power-on, because a large number of filter capacitors are arranged in a functional circuit, the instant charging current (also in a pulse current mode) is often very large, and the capacity in the LC filter capacitors is not enough, the voltage of a battery is pulled down, so that the phenomenon of power-failure reset of a system is caused.
As shown in fig. 11, R1, R2, R3, R4, R5, R6, Q1, and U5 constitute sensor excitation circuits, and the gate of Q1 is connected to Pin39 of the bluetooth main control chip U0 in the wireless soc module. The sensor excitation circuit output VS + is connected to the sensor anode through the transmitter electrical contact S +. VS _ REF is the precision reference voltage source output in the functional circuit power module. The outputs VS + and VS REF are calculated as follows,
VS _ SEL (corresponding to Db signal in fig. 1) is high:
wherein R4// R5 represents R4, and R5 represents parallel equivalent resistance
VS _ SEL (corresponding to Db signal in fig. 1) is low:
r7, R8, C5 and U6 constitute a conditioning circuit, which is essentially an I-V operation circuit and mainly 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 negative terminal of the sensor 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 and U6 power decoupling capacitors. C8 is a filter capacitor that controls the noise bandwidth of the circulating current signal.
Assume that the sensor current flowing into S-is I0ADC _ GLU and input I0The relationship of (1) is:
ADC_GLU＝VS_REF+I0*R8
since the sampled current is on the order of microamperes, R8 is preferably 1M Ω.
The precision 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 conventional solution is to use an external ADC chip, but the ADC is usually expensive. Therefore, the utility model discloses an ADC precision reinforcing circuit module, ADC precision reinforcing circuit adopt the noise injection method, can be on the basis of the fixed precision of the built-in ADC of wireless SOC module main control chip, and 1 bit is reinforceed to the sampling precision again. The sampling method comprises the following steps: injecting a noise voltage with the amplitude of 0 into a sampling signal, and performing ADC (analog to digital converter) sampling to obtain a result of Read 1; step2, injecting an amplitude value ofNoise voltage (V) ofADC_REFIs the ADC reference voltage, d is the target precision digit), ADC sampling is performed, and the result is Read 2; in step3, the final result is Read (Read1+ Read2)/2The resulting precision can be enhanced by 1 bit.
As shown in fig. 12, two stages of noise signals are injected above the sampling signals to perform respective sampling, and after averaging after sampling, the accuracy can be increased by 1 bit resolution.
The circuit for injecting the noise signal is realized by adopting an addition operation circuit, and each path of sampling needs one addition operation circuit. As shown, U8, R13, R14, R15 and R16 form a precision enhancing circuit for VS _ REF. U9, R17, R18, R19, R20 constitute a precision enhancement circuit for ADC _ GLU. The structure of each ADC precision enhancement circuit is the same. The precision enhancement circuit outputs ADC _ R and ADC _ G after filtering by a post-stage filter circuit consisting of R9R10C8C9C10, and the ADC _ R and ADC _ G are 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 has only 3V high-level or 0V low-level.
Take VS _ REF path as an example, let R13＝k*R14，R19＝k*R20Therefore, it isWherein k is 2d. When the actual precision of the ADC is 10 bits and the target precision is 11 bits, k should be a value close to 2048.
Step 1: bit11 outputs a low level, VBit11ADC sampling is performed at 0, resulting in Read 1;
step 2: bit11 outputs a high level, VBit11ADC sampling was performed at 3, resulting in Read 2;
step 3: the final result Read is (Read1+ Read2)/2, which is the result after enhancing the precision.
In this example, the standard conversion precision of ADC of the Bluetooth master control chip is 10 bits when no oversampling occurs, the reference voltage is calculated according to 1 (100%), and the precision is
Let the result register be a 12-bit register, with the result high bit aligned to the result register. Table 1 table 2 shows the calculation of the accuracy enhancement after signal injection.
TABLE 1.10 bit ADC and 11 bit ADC code tables
TABLE 2 ADC precision enhancement signal calculation example table
From table 2, it can be seen that the 1-bit sampling precision can be increased by injecting (superimposing) a noise signal on the sampled voltage signal in the method, summing the sampling results of the noise signal injected each time, and averaging the results.
As shown in fig. 13, the LC filter energy storage circuit can select a button battery with a 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 accordingly, a battery with a smaller capacity (volume) can be selected;
in the LC filtering energy storage circuit, V + V-is connected with the positive electrode and the negative electrode of the battery, and VDD _ NRF supplies power to a Bluetooth main control chip in the wireless SOC module.
L6, C34, C35, C36 and C37 form an LC filter tank circuit. Because the discharge capacity of the battery is related to the capacity, the pulse discharge capacity of a conventional small-capacity CR series button battery is about 5mA, and when a radio frequency event (wirelessly transmitting data or receiving data) occurs, the current load of the Bluetooth chip is as high as more than 12mA and far exceeds the pulse discharge capacity of the battery.
When the battery pulse discharge ability is not enough, can draw down battery both ends voltage, when the voltage is low excessively, can make bluetooth main control chip take place to reset, the short of electricity trouble of entire system. On the other hand, the repeated pulse current may damage the battery itself, i.e., the pulse current may cause the actual operation capacity of the battery to be much smaller than the nominal capacity.
Considering that the radio frequency event is intermittent, in this example, an inductance-capacitance filtering energy storage circuit is added, when no pulse current occurs, C34, C35, C36 and C37 mainly function as energy storage, when no radio frequency time occurs, the power consumption of the whole circuit is very small, therefore, the charging of the capacitor by the battery is larger than the discharging of the capacitor to the system circuit, and the redundant energy is stored in the capacitor. 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, the battery is in a relatively gentle discharging state in the whole working period, the voltage drop event is effectively inhibited, and the damage of the pulse current to the battery is prevented.
The inductor L6 mainly suppresses 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 at high frequency. When a pulse current occurs, L6 may prioritize battery discharge over battery discharge, i.e., the amount of power stored in the capacitor.
As shown in fig. 14, the wireless SOC module circuit, in this example, preferably has a bluetooth chip U0 as a 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 exciting and conditioning circuit and the precision enhancing circuit. A separate power supply method is adopted, and the principle of who works and who supplies power is adopted. When the functional circuit does not need to work, the electric quantity of the battery can not be consumed, and the power consumption is effectively reduced. In order to reliably electrify the functional circuit, a soft electrifying method is designed, the pulse current amplitude at the electrifying moment is effectively inhibited, and the emitter 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 16 MHz. The capacitors C21, C22 and crystal Y2 provide a low frequency clock source for the Bluetooth chip, and the crystal Y2 is preferably 32.768 kHz.
DV, DIO, DCK and DG are simulation ports and are used for simulating and programming programs. C23, C24, C25, C26, C29, C30 and C33 are power decoupling capacitors of the Bluetooth chip. L4, C31 and antenna ANT1 constitute a bluetooth radio frequency circuit for modulating radio signals.
The Pin37 of U0 is connected to the gate of the Q2 of the switch S1 circuit and is used for controlling the on-off of the power supply of the functional circuit. When the functional circuit is not needed to work, the 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 an ADC precision enhancement module circuit and are used for calculating blood glucose concentration.
The Pin6 of the U0 is connected to the positive pole 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.
The 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 case by a mosfet, to apply two levels of excitation to the sensor.
The above-mentioned embodiments further describe the objects, technical solutions and advantages of the present invention in detail, it should be understood that the above description is only the embodiments of the present invention, and is not intended to limit the present invention, and any modifications, equivalent substitutions, improvements and the like made within the spirit and principle of the present invention should be included in the scope of the present invention.
Claims (8)
1. Separation power supply developments blood sugar monitoring transmitter, its characterized in that: comprises an emitter (200) and a sensor base device (300); the sensor base device (300) comprises a base (302) and an adhesive tape (303), wherein the base (302) is positioned on the adhesive tape (303); the upper portion of the base (302) is provided with an opening, a battery jar (3021) and a groove (3024) are arranged in the base (302), a battery (304) and a battery cover (307) are installed in the battery jar (3021), a rotating base (309) is installed in the groove (3024), one side, close to the battery jar (3021), of the rotating base (309) is hinged in the groove (3024), a silica gel base (310) is arranged in the rotating base (309), a pair of conductive rubbers (311) are arranged in the silica gel base (310), a sensor (301) is arranged to penetrate through the silica gel base (310) and the rotating base (309), the sensor (301) can penetrate through the two conductive rubbers (311), one side, close to the battery jar (3021), of the groove (3024) is provided with an opening (3025), the adhesive (303) is provided with a hole, and the sensor (301) can penetrate through the openings (3025) and the adhesive (303); the transmitter (200) comprises a plastic package shell (202) and a circuit board assembly (201), wherein the plastic package shell (202) is covered on the base (302), the circuit board assembly (201) is installed inside the plastic package shell (202), four conductive pins are arranged on the circuit board assembly (201), and the conductive pins can contact the positive electrode and the negative electrode of the battery (304) and two conductive rubbers (311).
2. The separately powered ambulatory blood glucose monitoring transmitter of claim 1, further comprising: the silicon rubber base (310) is provided with a first conductive rubber hole (3101) and a second conductive rubber hole (3102), and the two conductive rubbers (311) are respectively arranged in the first conductive rubber hole (3101) and the second conductive rubber hole (3102); two square holes (3103) are further arranged in the silicon rubber seat (310), two conductive rubbers (311) and the two square holes (3103) are linearly distributed, and the sensor (301) penetrates through the two conductive rubbers (311).
3. The separately powered ambulatory blood glucose monitoring transmitter of claim 1, further comprising: two sides in the groove (3024) are respectively provided with a semicircular hole (3026), two sides of the end part of the rotating base (309) are respectively provided with a flexible extension bar (3091), the outer side of the extension bar (3091) is provided with a cylindrical shaft (3092), and the cylindrical shaft (3092) is arranged in the semicircular hole (3026) to rotate.
4. The separately powered ambulatory blood glucose monitoring transmitter of claim 1, further comprising: the battery comprises a battery body (304), wherein the positive electrode and the negative electrode of the battery body (304) are respectively provided with an electrode adapter (305), each electrode adapter (305) is provided with an electrode connecting piece (306), the battery cover (307) is provided with two round holes (3073), one round hole (3073) corresponds to one electrode connecting piece (306), and the electrode connecting piece (306) penetrates through the round holes (3073) and is partially arranged outside the battery cover (307).
5. The separately powered ambulatory blood glucose monitoring transmitter of claim 4, wherein: four conductive pins on wiring board subassembly (201) are two battery guide pins (2011) and two rubber guide pins (2012), and an electrode connecting piece (306) is connected respectively to two battery guide pins (2011), and a conductive rubber (311) is connected respectively to two rubber guide pins (2012).
6. The separately powered ambulatory blood glucose monitoring transmitter of claim 1, further comprising: the end part of the base (302) is provided with a base buckle opening (3023), and the end part of the plastic package shell (202) is provided with an edge boss (2021) inserted into the base buckle opening (3023); the side of the plastic package shell (202) is provided with a shell clamping groove (2022), and the inner side wall of the groove (3024) is provided with an elastic buckle (3027) clamped into the shell clamping groove (2022).
7. The separately powered ambulatory blood glucose monitoring transmitter of claim 1, further comprising: the battery jar (3021) is provided with a sealing strip (308) on one circle of the edge, and the silica gel base (310) is provided with a rib position (3104) on one circle of the edge.
8. A system of separately powered ambulatory blood glucose monitoring transmitters according to any of claims 1-7 and comprising: comprises an LC filtering energy storage module, a wireless SOC module, a functional circuit power supply module, a sensor excitation and conditioning module, an ADC precision enhancing module, a battery and a sensor, the positive pole and the negative pole of the battery are respectively connected with the LC filtering energy storage module through a circuit, a connecting line is arranged between the LC filtering energy storage module and the VDD end of the wireless SOC module, the connecting wire is provided with a double control switch which can be connected with the Da end of the wireless SOC module or the functional circuit power module, the functional circuit power module is connected with the sensor excitation and conditioning module through a circuit, the Db end of the wireless SOC module is also connected with the sensor excitation and conditioning module through a line, the wireless SOC module is provided with a built-in ADC module, the Dc end of the wireless SOC module and the built-in ADC module are both connected with the ADC precision enhancing module, the ADC precision enhancing module is connected with the sensor excitation and conditioning module through a line, and the positive electrode and the negative electrode of the sensor excitation and conditioning module are respectively connected with the sensor through a line.
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Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109998560A (en) * | 2019-04-30 | 2019-07-12 | 苏州百孝医疗科技有限公司 | Separation power supply Dynamic Blood Glucose Monitoring transmitter, system and signal sampling method |
| CN112120709A (en) * | 2020-09-27 | 2020-12-25 | 微泰医疗器械(杭州)有限公司 | Blood sugar monitoring device |
| CN113274003A (en) * | 2019-08-19 | 2021-08-20 | 上海移宇科技股份有限公司 | Intelligent detection device |
| WO2022199485A1 (en) * | 2021-03-23 | 2022-09-29 | 微泰医疗器械(杭州)股份有限公司 | Real-time blood glucose monitoring apparatus and manufacturing method therefor |
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2019
- 2019-04-30 CN CN201920621728.4U patent/CN210056040U/en active Active
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109998560A (en) * | 2019-04-30 | 2019-07-12 | 苏州百孝医疗科技有限公司 | Separation power supply Dynamic Blood Glucose Monitoring transmitter, system and signal sampling method |
| CN109998560B (en) * | 2019-04-30 | 2023-12-22 | 苏州百孝医疗科技有限公司 | Separated power supply dynamic blood glucose monitoring transmitter, system and signal sampling method |
| CN113274003A (en) * | 2019-08-19 | 2021-08-20 | 上海移宇科技股份有限公司 | Intelligent detection device |
| CN113274003B (en) * | 2019-08-19 | 2023-09-12 | 上海移宇科技股份有限公司 | Intelligent detection device |
| CN112120709A (en) * | 2020-09-27 | 2020-12-25 | 微泰医疗器械(杭州)有限公司 | Blood sugar monitoring device |
| WO2022199485A1 (en) * | 2021-03-23 | 2022-09-29 | 微泰医疗器械(杭州)股份有限公司 | Real-time blood glucose monitoring apparatus and manufacturing method therefor |
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