CN217138061U - Blood glucose monitoring circuit and medical equipment - Google Patents

Abstract

The utility model relates to a blood sugar monitoring circuit and medical equipment. The blood glucose monitoring circuit adopts the magnetic control switch to control the transmitter module to be powered on, the blood glucose monitoring device containing the blood glucose monitoring circuit can automatically start to monitor the blood glucose change of a user when the user wears the blood glucose monitoring device, the magnetic control switch is controlled by a magnet to be switched on and off, the influence of muscle shake or human body activity is not easily caused, the transmitter module is not easily powered off in the working process of the sensor module and the transmitter module, the restarting of the power failure is avoided, the wireless connection between the transmitter module and terminal equipment is not required to be reestablished, the stability of the blood glucose monitoring circuit is enhanced, the power consumption of a circuit system is favorably reduced, the electricity is saved, and the standby time of the transmitter module is prolonged. The medical device includes the blood glucose monitoring circuit.

Description

Blood glucose monitoring circuit and medical equipment

Technical Field

The utility model relates to the field of medical equipment, especially, relate to a blood sugar monitoring circuit and a medical equipment.

Background

Blood glucose monitoring is an important component in diabetes management, and the results of blood glucose monitoring are helpful for evaluating the degree of glucose metabolism disorder of a diabetic patient, specifying a blood glucose reduction scheme, and reflecting the treatment effect and guiding the adjustment of the treatment scheme. Blood glucose concentration is related to many factors such as exercise, diet, medication, etc. The traditional blood sugar monitoring method is blood collection monitoring, but the method cannot reflect the blood sugar map of a patient all day long, and a monitoring blind area exists in time. Therefore, in recent years, a dynamic blood sugar monitoring product has been developed, which can realize continuous blood sugar monitoring throughout the day and dynamic monitoring of blood sugar level of diabetic patients.

Although the existing scheme adopts the problem of continuous real-time monitoring of blood sugar, the existing scheme has the problems that firstly, the transmitter of the existing dynamic blood sugar monitoring device is started by using a metal disc of a sensor base as a switch to switch on a power supply bus of the transmitter, so that the power supply bus of the transmitter is easily powered off instantly due to muscle jitter or human body activity, the power consumption of a system is increased by restarting a transmitter circuit and reestablishing wireless connection, and the stability is poor; secondly, the electronic circuit module in the transmitter of current scheme is many, transmitter hardware system constructs too complicacy, lead to the whole consumption too big of transmitter, can take place before blood sugar sensor has not become invalid yet, the condition that the transmitter battery has run out, wear with blood sugar sensor connection again after the battery charges, cause blood sugar test data to be interrupted on the one hand like this, on the other hand has increased patient's operational burden, if increase the capacity of lithium cell alone, then increase the volume of transmitter again, the foreign body sensation when making the patient wear increases, also is not advisable.

Therefore, how to improve the service life and reliability of the transmitter without increasing the volume of the transmitter and the capacity of the battery, so as to realize convenient and low-cost dynamic blood glucose monitoring is a problem to be solved at present.

SUMMERY OF THE UTILITY MODEL

In order to improve the life and the reliability of transmitter, practice thrift the cost, the utility model provides a blood sugar monitoring circuit. A medical device is also provided.

An aspect of the utility model provides a blood sugar monitoring circuit, include:

the sensor module comprises a blood sugar sensor, and the blood sugar sensor is used for detecting the blood sugar level of a human body and outputting a corresponding electric signal; the transmitter module is disconnectably connected with the sensor module and comprises a battery, a plurality of power utilization units and a magnetic control switch arranged between the battery and the plurality of power utilization units, and the transmitter module is used for applying an excitation voltage to the blood glucose sensor, acquiring an electric signal output by the blood glucose sensor, processing the electric signal and generating the electric signal to reflect the measured value of the blood glucose level of the human body; when the magnetic control switch and the magnet approach to a preset degree, a circuit of the magnetic control switch is conducted, and the plurality of power utilization units are powered on.

In some embodiments, the plurality of power consuming units of the transmitter module comprises:

a sensor excitation unit for generating an excitation voltage to be applied to the blood glucose sensor; the sensor signal conditioning unit is used for acquiring an electric signal output by the blood glucose sensor, wherein the electric signal is an analog current signal and converting the analog current signal into a corresponding analog voltage signal; and the processor unit is used for acquiring and processing the analog voltage signal output by the sensor signal conditioning unit to obtain a measured value reflecting the blood glucose level of the human body and sending the measured value to the terminal equipment.

In some embodiments, the processor unit comprises:

the analog-to-digital converter is used for amplifying the analog voltage signal output by the sensor signal conditioning unit and converting the analog voltage signal into a digital voltage signal which corresponds to linearity; the filter is used for carrying out smooth filtering processing on the digital voltage signal output by the analog-to-digital converter to form a measured value reflecting the blood sugar level of the human body; and the wireless communication module is used for transmitting the measured value to the terminal equipment.

In some embodiments, the sensor excitation unit and the sensor signal conditioning unit are implemented using a dual-channel operational amplifier chip.

In some embodiments, the plurality of power consuming units within the transmitter module include a bias voltage control unit and a sensor excitation unit, the bias voltage control unit being configured to output respective control signals to the sensor excitation unit to adjust an excitation voltage applied to the blood glucose sensor at different operating periods of the blood glucose sensor.

In some embodiments, the bias voltage control unit includes a voltage dividing chip, and a first voltage dividing circuit and a second voltage dividing circuit connected to the voltage dividing chip, and the voltage dividing chip switches between the first voltage dividing circuit and the second voltage dividing circuit using an analog switch to divide voltage using one of the first voltage dividing circuit and the second voltage dividing circuit and obtain a corresponding divided voltage value, and the divided voltage value is output to the sensor excitation unit.

In some embodiments, the excitation voltage is set to: the value of the excitation voltage decreases after the blood glucose sensor is implanted in the human body for more than the activation period relative to the activation period after the blood glucose sensor is implanted in the human body.

In some embodiments, the power utilization unit within the transmitter module further comprises: the voltage stabilizing unit is connected with the bias voltage control unit and used for generating a reference voltage based on the output of the battery and providing the reference voltage to the bias voltage control unit as a divided reference voltage source; and/or the battery capacity measuring unit is used for measuring the residual capacity of the battery and feeding back the residual capacity to the processor unit.

In some embodiments, the transmitter module comprises a primary output circuit and a secondary output circuit which are connected in sequence at the output end of the battery, the output node of the primary output circuit is behind the magnetic control switch and in front of the plurality of power utilization units, and the output voltage of the primary output circuit is greater than the voltage of the secondary output circuit; the processor unit and the battery electric quantity measuring unit are connected to the output voltage of the primary output circuit to be powered on, and the sensor signal conditioning unit, the bias voltage control unit and the voltage stabilizing unit are connected to the output voltage of the secondary output circuit to be powered on.

In some embodiments, the battery is a disposable battery.

Another aspect of the present invention is to provide a medical device, which employs the blood glucose monitoring circuit described in the previous embodiment.

Has the advantages that:

the utility model provides a blood sugar monitoring circuit has adopted the scheme of electricity on the magnetic control switch, and the automatic blood sugar that begins monitoring user when the user wears changes, has saved the switch contact of transmitter with the base, has strengthened the reliability. Further, the blood glucose monitoring circuit also has the following advantages:

firstly, the excitation voltage is adjusted through the bias voltage control unit, so that on one hand, the electrochemical reaction of a sensor probe can be started and reaches a relatively stable state according to the wearing time of the blood glucose monitoring device, the adaptive time of the initial operation of the blood glucose monitoring device is shortened, the measured value can be obtained quickly, on the other hand, the reaction speed of the glucolase can be controlled well, the glucolase is prevented from being consumed too quickly, the effective working time of the blood glucose sensor is ensured, and the interference factors of other components in interstitial fluid can be reduced to the minimum;

secondly, the disposable battery is used, a power management module required by using a rechargeable battery and a charging interface required to be reserved by the transmitter are omitted, the size of the transmitter module is reduced, and the user operation is simplified;

thirdly, a processor with a built-in analog-to-digital conversion unit (ADC) and a wireless communication module is selected, so that the circuit integration level is high;

fourth, adopt the binary channels fortune to put as sensor excitation and sampling conditioning circuit, adopt the current-limiting measure at the chip supply end in addition, all help reducing the chip consumption, can prolong the time of endurance of transmitter module, under the condition that does not increase the volume of transmitter module (battery capacity does not increase promptly), the life-span of transmitter module is expected to cover more than one sensor life cycle (blood glucose sensor is disposable), and under the condition that battery power exhausts, can change the battery rapidly, realize convenient, continuous, reliable, low-cost dynamic blood glucose monitoring.

The utility model provides a medical equipment includes above-mentioned blood sugar monitoring circuit, have with the similar advantage of blood sugar monitoring circuit.

Drawings

Fig. 1 is a schematic circuit diagram of a blood glucose monitoring circuit according to an embodiment of the present invention.

Fig. 2 is a schematic circuit diagram of the blood glucose monitoring circuit according to the embodiment of the present invention for obtaining the primary output voltage.

Fig. 3 is a schematic diagram of a circuit for obtaining a secondary output voltage and a voltage stabilizing unit of the blood glucose monitoring circuit according to the embodiment of the present invention.

Fig. 4 is a schematic circuit diagram of the blood glucose sensor, the sensor excitation unit, the sensor signal conditioning unit and the bias voltage control unit in the blood glucose monitoring circuit according to the embodiment of the present invention.

Fig. 5 is a schematic circuit diagram of a processor unit and a sensor signal conditioning unit in a blood glucose monitoring circuit according to an embodiment of the present invention.

Fig. 6 is a schematic circuit diagram of a battery power measuring unit in a blood glucose monitoring circuit according to an embodiment of the present invention.

Description of reference numerals:

110-a sensor module; 111-a magnet; 112-a blood glucose sensor; 120-a transmitter module; 121-a battery; 122-a magnetic control switch; 123-a sensor excitation unit; 124-sensor signal conditioning unit; 125-a processor unit; 126-bias voltage control unit; 127-a voltage stabilizing unit; 128-battery charge measuring unit.

Detailed Description

The blood glucose monitoring circuit and the medical device of the present invention will be described in further detail with reference to the accompanying drawings and specific embodiments. The advantages and features of the present invention will become more apparent from the following description. It is to be understood that the drawings in the specification are in simplified form and are not to be taken in a precise scale, for the purpose of facilitating and distinctly claiming the embodiments of the present invention.

Fig. 1 is a schematic circuit diagram of a blood glucose monitoring circuit according to an embodiment of the present invention. Referring to fig. 1, embodiments of the present invention relate to a blood glucose monitoring circuit that includes asensor module 110 and a transmitter module 120 that are disconnectably connected together.

Thesensor module 110 includes ablood glucose sensor 112, and theblood glucose sensor 112 is implantable for detecting a blood glucose level of a human body in an implanted state and outputting a corresponding electrical signal. The probe of theblood glucose sensor 112 generates a current analog signal by detecting the oxidation-reduction reaction of the glucose in the interstitial fluid of the human tissue and the subcutaneous intercellular fluid of the user, and theblood glucose sensor 112 may have a sensor structure disclosed in the art.

The transmitter module 120 is used for applying an excitation voltage to theblood glucose sensor 112 and collecting an electrical signal output by theblood glucose sensor 112, and after processing, generating a measurement value reflecting the blood glucose level of the human body and sending the measurement value to the terminal device. The transmitter module 120 includes abattery 121 and a plurality of power using units connected to thebattery 121, and when the transmitter module 120 is connected to thesensor module 110, theblood glucose sensor 112 in thesensor module 110 is connected to at least one power using unit in the transmitter module 120, thereby being connected to thebattery 121. Thebattery 121 is used to provide energy input (i.e., power) to the plurality of power consuming units in the transmitter module 120 and also to provide energy input (i.e., power) to theblood glucose sensor 112 when theblood glucose sensor 112 is connected to the transmitter module 120.

In the embodiment of the present invention, thesensor module 110 further includes a magnet 111. The magnet 111 may be implanted with theblood glucose sensor 112 under the skin of a user whose blood glucose is to be monitored, and the magnet 111 may be provided on the base of theblood glucose sensor 112. The transmitter module 120 further includes amagnetic switch 122 disposed at an output end of thebattery 121, wherein themagnetic switch 122 controls an output of thebattery 121, that is, when a circuit of themagnetic switch 122 is turned on, the power consumption unit in the transmitter module 120 is powered by thebattery 121 to operate, and when the circuit of themagnetic switch 122 is turned off, the power consumption unit in the transmitter module 120 stops operating. The magnetically controlledswitch 122 may include a normally open reed switch or a normally closed reed switch. The magnet 111 in thesensor module 110 is used to trigger themagnetic switch 122 to be turned on, that is, when themagnetic switch 122 and the magnet 111 approach to a preset extent (i.e., enter a set range around the magnet 111), the circuit is turned on by the magnetic field of the magnet 111, and when the distance between themagnetic switch 122 and the magnet 111 exceeds the preset extent, themagnetic switch 122 is not triggered by the magnet 111 and the circuit is turned off. Specifically, when blood glucose monitoring is required, thesensor module 110 is implanted into a human body, the transmitter module 120 is connected to thesensor module 110 through corresponding contacts, and themagnetic switch 122 is close to the magnet 111 inside thesensor module 110 until themagnetic switch 122 is electrically connected, so that thebattery 121 can supply power to each power unit in the transmitter module 120 and theblood glucose sensor 112 in thesensor module 110, and blood glucose monitoring is automatically started.

In the blood sugar monitoring circuit, themagnetic control switch 122 is adopted to control the transmitter module 120 to be powered on, when a user wears a blood sugar monitoring device comprising the blood sugar monitoring circuit, the blood sugar change of the user can be automatically monitored, switch contacts do not need to be arranged on the transmitter module 120 and a blood sugar sensor base, because the on-off of themagnetic control switch 122 is only related to a magnetic field, the on-off of themagnetic control switch 122 is controlled by the magnet 111, the blood sugar monitoring circuit is not easily influenced by muscle shake or human body activity, in the working process of thesensor module 110 and the transmitter module 120, the transmitter module 120 is not easily powered off, the power-off restarting is avoided, the wireless connection between the transmitter module 120 and a terminal device is not needed to be reestablished, the stability of the blood sugar monitoring circuit is enhanced, the power consumption of a circuit system is reduced, the electricity is saved, and the standby time of the transmitter module 120 is prolonged, thereby contributing to prolonging the inventory shelf life of blood glucose test products employing the blood glucose monitoring circuit.

In the transmitter module 120, thebattery 121 may be a disposable battery, and compared with a rechargeable battery, a power management module and a charging interface required for using the rechargeable battery are omitted, which is helpful for reducing the size of the transmitter module 120 and reducing power consumption, and simplifies user operations. Thebattery 121 is, for example, a lithium manganese button battery with a rated power of 70 mAh. Thebattery 121 may be installed in a dedicated battery box for easy replacement.

The transmitter module 120 may be fabricated as a package wrapped in a biocompatible material, in which thebattery 121, themagnetic switch 122, and the power consuming units are located, and which exposes only the contacts for connection with thesensor module 110. Themagnetic switch 122 need not be exposed because the magnetic field can pass through the packaging material of the package. Correspondingly, thesensor module 110 also has electrode terminals corresponding to the contacts on the surface of the transmitter module 120, and the electrode terminals are connected to theblood glucose sensor 112 in thesensor module 110 to drive theblood glucose sensor 112 to operate. When thesensor module 110 is implanted in the body, the electrode terminals on thesensor module 110 are exposed for connection with the contacts on the transmitter module 120, and the electrode terminals and the corresponding contacts may be connected by suitable connectors. As an example, the contacts of the surface of the transmitter module 120 for connecting thesensor module 110 include a reference electrode contact RE, a working electrode contact WE and an auxiliary electrode contact CE, and thesensor module 110 has three electrode terminals corresponding to the three contacts.

Alternatively, it may be provided that thebattery 121 provides different supply voltages to the plurality of power consuming units within the transmitter module 120 to reduce power consumption by reducing the dynamic range of chip operation within the transmitter module 120. Fig. 2 is a schematic circuit diagram of the blood glucose monitoring circuit according to the embodiment of the present invention for obtaining the primary output voltage. Fig. 3 is a schematic diagram of a circuit for obtaining a secondary output voltage and a voltage stabilizing unit of the blood glucose monitoring circuit according to the embodiment of the present invention. Referring first to fig. 2, the transmitter module 120 of the blood glucose monitoring circuit includes a primary output circuit and a secondary output circuit connected in sequence at the output end of a battery 121(BT), the output node of the primary output circuit is disposed behind amagnetic switch 122 and in front of the plurality of power consumption units, the output voltage of thebattery 121 is denoted as V _ BAT, themagnetic switch 122 is connected to thebattery 121, and the circuit of themagnetic switch 122 includes capacitors C1, C2, C3 and a small normally open reed switch F1. The voltage at the output node of the primary output circuit is the power output of thebattery 121 and is referred to as a first output voltage VDD _ nRF. Referring to fig. 3, in this embodiment, the output node of the primary output circuit is connected to a secondary output circuit, the secondary output circuit includes a current limiting resistor R1 connected to the output node of the primary output circuit, and after current limiting output is performed through a current limiting resistor R1, an output of the secondary output circuit is formed, and is denoted as a second output voltage VDD. That is, the first output voltage VDD _ nRF and the second output voltage VDD are obtained by thebattery 121 and the primary output circuit and the secondary output circuit, respectively, so that each power consuming unit in the transmitter module 120 can be designed to be powered by one of the first output voltage VDD _ nRF and the second output voltage VDD. As an example, among the plurality of power consuming units in the transmitter module 120 described below, theprocessor unit 125 and the batterylevel measurement unit 128 are powered on when connected to the first output voltage VDD _ nRF, and the sensorsignal conditioning unit 124, the biasvoltage control unit 126 and thevoltage stabilization unit 127 are powered on when connected to the second output voltage VDD.

Referring to fig. 1, the plurality of power consuming units within the transmitter module 120 comprises asensor excitation unit 123, a sensorsignal conditioning unit 124 and aprocessor unit 125, wherein thesensor excitation unit 123 is connected to theblood glucose sensor 112 for generating an excitation voltage to be applied to theblood glucose sensor 122. The sensorsignal conditioning unit 124 is configured to collect an electrical signal output by theblood glucose sensor 122, which may be an analog current signal, and convert the analog current signal into a corresponding analog voltage signal after performing signal conditioning on the analog current signal. In this embodiment, theblood glucose sensor 122 detects interstitial fluid of human tissue and outputs a weak analog current signal to the sensorsignal conditioning unit 124, and the sensorsignal conditioning unit 124 processes the analog current signal based on the received analog current signal to obtain an analog voltage signal corresponding to the acquired analog current signal. Theprocessor unit 125 is configured to obtain and process the analog voltage signal output by the sensorsignal conditioning unit 124, obtain a measurement value reflecting the blood glucose level of the human body, and send the measurement value to the terminal device. Theprocessor unit 125 may also be used to control thesensor excitation unit 123 to increase or decrease the excitation voltage applied to theblood glucose sensor 122. Theprocessor unit 125 may be implemented using a Microprocessor (MCU) chip.

Fig. 4 is a schematic circuit diagram of a blood glucose sensor, a sensor excitation unit, a sensor signal conditioning unit and a bias voltage control unit in a blood glucose monitoring circuit according to an embodiment of the present invention. Referring to fig. 4, as an example, thesensor excitation unit 123 is formed by a 1-stage operational amplifier circuit, and in this embodiment, for example, a dual-channel operational amplifier chip (preferably, low power consumption, model such as LPV802) is used to implement thesensor excitation unit 123. Specifically, thesensor excitation unit 123 implements a sensor excitation circuit using the first-stage channel of the dual-channel op-amp chip, in order to obtain an excitation voltage to be applied to theblood glucose sensor 112, and thesensor excitation unit 123 further includes a low-pass filter network composed of a resistor R4 and a capacitor C6, in order to eliminate an ac signal above a set value (e.g., 0.8 Hz). The electrodes of theblood glucose sensor 112 are connected to thesensor excitation unit 123 via three contacts RE, CE, WE. After thesensor excitation unit 123 applies a suitable excitation voltage to theblood glucose sensor 112, theblood glucose sensor 112 starts to operate, and generates a weak current signal according to the blood glucose level of the user, which reflects the blood glucose level of the human body.

Referring to fig. 4, the sensorsignal conditioning unit 124 is formed by a 1-stage operational amplifier circuit, and in this embodiment, the sensorsignal conditioning unit 124 is implemented by a dual-channel low-power-consumption operational amplifier chip (model, for example, LPV802) for implementing thesensor excitation unit 123. Specifically, the sensorsignal conditioning unit 124 implements a current/voltage conversion (i.e., I/V conversion) circuit using the second-stage channel of the dual-channel operational amplifier chip, and converts a micro-current (e.g., about 0 to 100nA) output by theblood glucose sensor 112 into a corresponding voltage signal (e.g., about 0 to 50mV) through the resistor R7, and the sensorsignal conditioning unit 124 further includes a low-pass filter network composed of a resistor R5 and a capacitor C9, so as to eliminate an ac signal above a set value (e.g., 3 Hz).

Fig. 5 is a schematic circuit diagram of a processor unit and a sensor signal conditioning unit in a blood glucose monitoring circuit according to an embodiment of the present invention. Referring to fig. 5, theprocessor unit 125 may use, for example, an MCU chip with an internal analog-to-digital converter ADC (preferably with high precision), a filter, and a wireless communication module, for example, an MCU chip with a model number nRF52810, and reference may be made to a chip manual for describing each element and symbol in the MCU chip shown in fig. 5, where VDD _ nRF represents accessing the first output voltage. An analog-to-digital converter in theprocessor unit 125 is used to amplify and convert the analog voltage signal output by the sensorsignal conditioning unit 124 into a linearly corresponding digital voltage signal. The filter in theprocessor unit 125 is used to perform a smoothing filtering process on the digital voltage signal output by the analog-to-digital converter to form a measurement value reflecting the blood glucose level of the human body. For example, when detecting the current blood glucose level, the digital voltage signal obtained by continuously collecting ten times is subjected to smoothing filtering processing, and the maximum value and the minimum value are removed and averaged to obtain the measurement value, where the measurement value is a voltage value. In addition, in order to facilitate direct reading of the blood glucose level from the terminal device, before or after a signal is output to the terminal device (e.g. a mobile phone, a computer, a server, or the like) by using the wireless communication module (e.g. "bluetooth 4.0" in fig. 1), the measured value is converted into a corresponding current value, and the blood glucose level of the current test can be obtained by substituting the current value corresponding to the measured value into a corresponding blood glucose calculation formula.

For example, referring to fig. 4 and 5, after acquiring the analog voltage signal output by the sensorsignal conditioning unit 124, theprocessor unit 125 performs analog-to-digital conversion on the analog signal output by the sensorsignal conditioning unit 124 by using the analog-to-digital converter ADC. The internal gain of the analog-to-digital converter ADC is set to 6, for example, after a micro-current analog signal of 0 to 100nA output by theblood glucose sensor 112 is converted into a voltage analog signal of 0 to 50mV by the sensorsignal conditioning unit 124, the voltage analog signal is converted into a digital voltage signal of 0 to 300mV in a linear correspondence relationship by the analog-to-digital converter ADC built in theprocessor unit 125, and then the digital voltage signal obtained by the analog-to-digital converter ADC is processed by a filter to form a measurement value, and the effective voltage value is converted into a current value, and then the current value is sent to the terminal device through the wireless communication module provided by the terminal device.

Referring to fig. 1 and 4, in the present embodiment, the emitter module 120 further includes a biasvoltage control unit 126, and the biasvoltage control unit 126 is configured to output corresponding control signals to thesensor excitation units 123 respectively during different operation periods of theblood glucose sensor 112, so as to adjust the excitation voltage applied to theblood glucose sensor 112. For example, the excitation voltage may be set to: the value of the excitation voltage decreases beyond the activation period after theblood glucose sensor 112 is implanted in the body relative to the activation period after the blood glucose sensor is implanted in the body. The biasvoltage control unit 126 is connected to theprocessor unit 125 and thesensor excitation unit 123, and the biasvoltage control unit 126 can output the corresponding control signal according to the instruction of theprocessor unit 125.

Referring to fig. 4, as an example, the biasvoltage control unit 126 includes a voltage dividing chip (model number is TS2a5223, for example) for dividing the second output voltage VDD output by thebattery 121, and an NO2 terminal and an NC2 terminal of the voltage dividing chip are respectively connected to the first voltage dividing circuit and the second voltage dividing circuit, so that the biasvoltage control unit 126 can select one of the first voltage dividing circuit and the second voltage dividing circuit to divide the voltage during different operation periods of theblood glucose sensor 112, obtain a divided voltage value and send the divided voltage value to thesensor excitation unit 123. For example, the first voltage division circuit comprises resistors R13, R14, R15 and R16, wherein R13 and R14 are connected in series between the NO2 terminal of the voltage division chip and the ground, and R15 and R16 are connected in series between the NC2 terminal of the voltage division chip and the ground. The second voltage division circuit comprises resistors R9, R10, R11 and R12, wherein R9 and R10 are connected in series between an NC2 terminal of the voltage division chip and ground, and R11 and R12 are connected in series between an NC2 terminal of the voltage division chip and a reference voltage VREF (the reference voltage can be obtained by a voltage stabilization unit described later). The voltage dividing chip may switch between the first voltage dividing circuit and the second voltage dividing circuit by using an analog switch, so as to divide the voltage by using one of the first voltage dividing circuit and the second voltage dividing circuit and obtain a corresponding voltage dividing value.

An example of the process of obtaining the partial pressure values at different operating periods of theblood glucose sensor 112 is described below. In one embodiment, when thesensor module 110 is just implanted in a human body within 1 hour, i.e., during the activation period, the biasvoltage control unit 126 may switch to the first voltage dividing circuit according to the instruction of theprocessor unit 125, obtain a first voltage dividing value, and form a corresponding output signal to be output to thesensor excitation unit 123, so that thesensor excitation unit 123 forms an excitation voltage applied between the WE electrode terminal and the RE electrode terminal of theblood glucose sensor 112, for example, the excitation voltage between the WE electrode terminal and the RE electrode terminal corresponding to the first voltage dividing value is 0.7V. When thesensor module 110 is implanted in the human body for more than 1 hour, the biasvoltage control unit 126 switches to the second voltage dividing circuit according to the instruction of theprocessor unit 125, obtains a second voltage dividing value, and forms a corresponding output signal to be output to thesensor excitation unit 123, so that thesensor excitation unit 123 forms an excitation voltage applied between the WE electrode terminal and the RE electrode terminal of theblood glucose sensor 112, for example, the excitation voltage between the WE electrode terminal and the RE electrode terminal corresponding to the second voltage dividing value is 0.35V. The reason why different partial pressure values are adopted in different working periods of theblood glucose sensor 112 is that a hydration activation process is required within a certain time (1 hour in this embodiment, set as required in practice) when thesensor module 110 just enters the interstitial fluid of the human tissue, and an example of a pressurization parameter of the excitation voltage between the WE electrode terminal and the RE electrode terminal required in this process is 0.7V (which can be set as required in practice). After thesensor module 110 enters the interstitial fluid of the human body for a certain time, the reaction speed of the glucolase at the probe can be controlled better by reducing the excitation voltage (even if the partial pressure value output by the biasvoltage control unit 126 is reduced), so that the glucolase is not consumed too fast, and the effective working time of the blood glucose sensor (for example, more than 14 days) is ensured, and the interference factors of other components in the interstitial fluid can be reduced to the minimum by reducing the partial pressure value, and the pressurization parameter of the excitation voltage between the WE electrode terminal and the RE electrode terminal required in the process is exemplified by half of the initial time period, namely 0.35V (which can be set as required in practice).

Referring to fig. 1 and 3, the power utilization unit in the transmitter module 120 may further include avoltage regulation unit 127, thevoltage regulation unit 127 is connected to the biasvoltage control unit 126, and thevoltage regulation unit 127 is configured to generate a reference voltage based on the output of thebattery 121 and provide the reference voltage to the biasvoltage control unit 126. As shown IN fig. 3, thevoltage regulator unit 127 includes, for example, a voltage regulator chip Q1 (for example, model REF3312), an input terminal (IN) of which is connected to the output node (VDD) of the secondary output circuit, and an output terminal (OUT) of which outputs a reference voltage VREF to the biasvoltage control unit 126 as a divided reference voltage source, and the reference voltage VREF also serves as a baseline of the analog voltage signal output by the biasvoltage control unit 126. Thevoltage stabilizing unit 127 further includes a capacitor C4 provided between the output node of the secondary output circuit and the ground, and capacitors C5, C4 and C5 provided between the output node of the reference voltage VREF and the ground, which are power supply filter capacitors.

Referring to fig. 1, the power utilization unit in the transmitter module 120 may further include a batterylevel measurement unit 128, and the batterylevel measurement unit 128 is used for measuring the remaining power level of thebattery 121 and feeding back the measured power level to theprocessor unit 125. Fig. 6 is a schematic circuit diagram of a battery power measuring unit in a blood glucose monitoring circuit according to an embodiment of the present invention. As an example, the batterylevel measuring unit 128 divides the output voltage of the battery 121 (here, the output voltage of thebattery 121 is, for example, the first output voltage VDD _ nRF obtained by the above-described primary output circuit) using a voltage dividing resistor circuit, and referring to fig. 6, R2 and R3 are connected in series between the first output voltage VDD _ nRF and ground, and the voltage of the series node is a divided voltage, that is, the voltage (for example, 2V to 3V) of thebattery 121 is divided into a dc voltage ADC _ BAT (for example, 0.36V to 0.54V). The dc voltage ADC _ BAT is collected by theprocessor unit 125, as shown in fig. 1, theprocessor unit 125 may include more than one analog-to-digital converter ADC therein, and theprocessor unit 125 may collect the dc voltage ADC _ BAT through another analog-to-digital converter ADC different from the one for collecting the output signal of theblood glucose sensor 112 to determine the remaining power of thebattery 121 in the transmitter module 120. In the batterycapacity measuring unit 128, the capacitor C6 and the resistor R3 form a low-pass filter network.

The blood glucose monitoring circuit of the above embodiment can be used for dynamic or static blood glucose detection, because the scheme of power-on of the magnetic control switch is adopted, the emitter module 120 is not easy to power down, and is particularly suitable for dynamic blood glucose detection, and under the condition that the volume of the emitter module 120 is not increased (namely, the battery capacity is not increased), the service life of the emitter module 120 is prolonged (more than one blood glucose sensor service cycle is expected to be covered), under the condition that the electric quantity of the battery is exhausted, the battery is convenient to replace rapidly, and the dynamic blood glucose monitoring with convenience, continuity, reliability and low cost is realized. Furthermore, by further optimizing the configuration of the transmitter module 120 of the blood glucose monitoring circuit, the following effects can also be achieved: firstly, the emitter module 120 is provided with a bias voltage control unit 126 to adjust the excitation voltage applied to the blood glucose sensor 112 through the bias voltage control unit 126, so that on one hand, the electrochemical reaction at the probe of the blood glucose sensor can be started and reach a relatively stable state according to the wearing time of the blood glucose monitoring device including the blood glucose monitoring circuit, the adaptation time of the initial operation of the blood glucose monitoring device can be shortened, the measured value can be obtained quickly, on the other hand, the reaction speed of the glucolase can be well controlled, so that the reaction speed is not consumed too fast, the effective working time of the blood glucose sensor can be ensured, and the interference factors of other components in interstitial fluid can be reduced to the minimum; secondly, the transmitter module 120 adopts a disposable battery, which saves a power management module and a charging interface required by using a rechargeable battery, is beneficial to reducing the volume of the transmitter module, and simplifies the user operation; thirdly, the offset voltage control unit 126 selects the processor unit 125 with the built-in analog-to-digital converter ADC and the wireless communication module, and the circuit integration level is high; fourthly, the transmitter module 120 adopts a dual-channel operational amplifier chip to realize the sensor excitation unit 123 and the sensor signal conditioning unit 124, and the second output voltage VDD of the battery 121 is connected to the power supply terminal of the chip for current limiting, so that the power consumption of the chip is reduced, and the endurance time of the transmitter module 120 can be prolonged. Experiments show that by using the blood glucose monitoring device comprising the blood glucose monitoring circuit, thebattery 121 of the emitter module 120 is a lithium manganese button battery, the average output current which is output by the emitter module 120 and reflects the blood glucose level of a human body is actually measured to be about 35.6 muA (in a 3V stable state) under a normal working state, and the cruising ability of the emitter module 120 to dynamic blood glucose monitoring can be actually measured to be more than 60 days.

The embodiment of the utility model provides a still relate to a medical equipment, medical equipment includes the blood sugar monitoring circuit of above-mentioned embodiment description. The medical device is, for example, a blood glucose monitor, or may also be a multifunctional medical device with blood glucose monitoring functionality. The medical device comprises asensor module 110 and a transmitter module 120, which are disconnectable or connectable to each other in the blood glucose monitoring circuit described above, by means of which a valid digital signal reflecting the blood glucose level of a human body can be obtained. In addition, the medical device may include at least one terminal device, and the transmitter module 120 may transmit the valid digital signal reflecting the blood glucose level of the human body or the blood glucose data obtained based on the valid digital signal to the terminal device by using the wireless communication module built in theprocessor module 125, and the terminal device may also convert the obtained valid digital signal reflecting the blood glucose level of the human body into a blood glucose value for the user to refer to. Because the blood sugar monitoring circuit is provided with the magnetic control switch, the blood sugar change of a user can be automatically monitored when the user wears the blood sugar monitoring circuit, the operation is convenient, the energy consumption can be reduced by optimizing the circuit arrangement of the emitter module 120, the endurance time of the emitter module 120 is prolonged, and the medical equipment has better performance.

The above description is only for the preferred embodiment of the present invention and is not intended to limit the scope of the claims of the present invention, and any person skilled in the art can use the above disclosed method and technical contents to make possible changes and modifications to the technical solution of the present invention without departing from the spirit and scope of the present invention, and therefore, any simple modification, equivalent change and modification made to the above embodiments by the technical substance of the present invention all belong to the protection scope of the technical solution of the present invention.

Claims (11)

1. A blood glucose monitoring circuit, comprising:

the sensor module comprises a blood sugar sensor, and the blood sugar sensor is used for detecting the blood sugar level of a human body and outputting a corresponding electric signal;

the transmitter module is disconnectably connected with the sensor module and comprises a battery, a plurality of power utilization units and a magnetic control switch arranged between the battery and the plurality of power utilization units, and the transmitter module is used for applying an excitation voltage to the blood glucose sensor, acquiring an electric signal output by the blood glucose sensor, processing the electric signal and generating the electric signal to reflect the measured value of the blood glucose level of the human body;

when the magnetic control switch and the magnet approach to a preset degree, a circuit of the magnetic control switch is conducted, and the plurality of power utilization units are powered on.

2. The blood glucose monitoring circuit of claim 1 wherein the plurality of power cells of the transmitter module comprises:

a sensor excitation unit for generating an excitation voltage applied to the blood glucose sensor;

the sensor signal conditioning unit is used for acquiring an electric signal output by the blood glucose sensor, wherein the electric signal is an analog current signal and converting the analog current signal into a corresponding analog voltage signal;

and the processor unit is used for acquiring and processing the analog voltage signal output by the sensor signal conditioning unit to obtain a measured value reflecting the blood glucose level of the human body and sending the measured value to the terminal equipment.

3. The blood glucose monitoring circuit of claim 2, wherein the processor unit comprises:

the analog-to-digital converter is used for amplifying the analog voltage signal output by the sensor signal conditioning unit and converting the analog voltage signal into a digital voltage signal which corresponds to linearity;

the filter is used for carrying out smooth filtering processing on the digital voltage signal output by the analog-to-digital converter to form a measured value reflecting the blood sugar level of the human body;

and the wireless communication module is used for transmitting the measured value to the terminal equipment.

4. The blood glucose monitoring circuit of claim 2 wherein the sensor driver unit and the sensor signal conditioning unit are implemented using dual channel op-amp chips.

5. The blood glucose monitoring circuit of claim 2, wherein the plurality of power consuming units in the transmitter module comprise a bias voltage control unit and a sensor excitation unit, the bias voltage control unit is configured to output corresponding control signals to the sensor excitation unit respectively during different operation periods of the blood glucose sensor to adjust the excitation voltage applied to the blood glucose sensor.

6. The blood glucose monitoring circuit of claim 5, wherein the bias voltage control unit comprises a voltage dividing chip and a first voltage dividing circuit and a second voltage dividing circuit connected to the voltage dividing chip, the voltage dividing chip switches between the first voltage dividing circuit and the second voltage dividing circuit using an analog switch to divide voltage using one of the first voltage dividing circuit and the second voltage dividing circuit and obtain a corresponding divided voltage value, and the divided voltage value is output to the sensor excitation unit.

7. The blood glucose monitoring circuit of claim 5, wherein the excitation voltage is set to: the value of the excitation voltage decreases after the blood glucose sensor is implanted in the human body for more than the activation period relative to the activation period after the blood glucose sensor is implanted in the human body.

8. The blood glucose monitoring circuit of claim 6, wherein the power-consuming unit within the transmitter module further comprises:

the voltage stabilizing unit is connected with the bias voltage control unit and used for generating a reference voltage based on the output of the battery and providing the reference voltage to the bias voltage control unit as a divided reference voltage source; and/or the presence of a gas in the gas,

and the battery electric quantity measuring unit is used for measuring the residual electric quantity of the battery and feeding back the residual electric quantity to the processor unit.

9. The blood glucose monitoring circuit of claim 8, wherein the transmitter module comprises a primary output circuit and a secondary output circuit connected in series at the output of the battery, the output node of the primary output circuit is after the magnetic switch and before the plurality of power consuming units, and the output voltage of the primary output circuit is greater than the voltage of the secondary output circuit; the processor unit and the battery electric quantity measuring unit are connected to the output voltage of the primary output circuit to be powered on, and the sensor signal conditioning unit, the bias voltage control unit and the voltage stabilizing unit are connected to the output voltage of the secondary output circuit to be powered on.

10. Blood glucose monitoring circuit according to one of the claims 1 to 9, characterized in that the battery is a disposable battery.

11. A medical device, characterized in that a blood glucose monitoring circuit according to any of claims 1 to 10 is used.

Images