CN119770035B - Blood glucose monitoring devices and methods - Google Patents
Blood glucose monitoring devices and methodsInfo
- Publication number
- CN119770035B CN119770035B CN202411874132.7A CN202411874132A CN119770035B CN 119770035 B CN119770035 B CN 119770035B CN 202411874132 A CN202411874132 A CN 202411874132A CN 119770035 B CN119770035 B CN 119770035B
- Authority
- CN
- China
- Prior art keywords
- module
- voltage value
- sensor
- value
- voltage
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Landscapes
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
本发明公开了一种血糖监测装置和方法，其中，装置中的组织液聚集模块连接于控制模块和第一传感器之间，用于在控制模块的控制下聚集皮下组织液，第一传感器用于与该所聚集的皮下组织液的皮肤表面发生电化学反应输出第一电流，第二传感器与参考电极连接，用于与参考电极所贴合皮肤表面发生电化学反应输出第二电流，第一电压检测模块连接于第一传感器和控制模块之间，用于监测第一电流的第一电压值，将第一电压值发送至控制模块，第二电压检测模块连接于第二传感器和控制模块之间，用于监测第二电流的第二电压值，将第二电压值发送至控制模块，控制模块用于根据第一电压值和第二电压值获取血糖浓度值。
This invention discloses a blood glucose monitoring device and method. The device includes a tissue fluid aggregation module connected between a control module and a first sensor, used to aggregate subcutaneous tissue fluid under the control of the control module. The first sensor generates a first current by reacting electrochemically with the skin surface of the aggregated subcutaneous tissue fluid. A second sensor is connected to a reference electrode and generates a second current by reacting electrochemically with the skin surface to which the reference electrode is attached. A first voltage detection module is connected between the first sensor and the control module, used to monitor the first voltage value of the first current and send the first voltage value to the control module. A second voltage detection module is connected between the second sensor and the control module, used to monitor the second voltage value of the second current and send the second voltage value to the control module. The control module obtains a blood glucose concentration value based on the first and second voltage values.
Description
Technical Field
The invention relates to the technical field of medical health monitoring, in particular to a blood glucose monitoring device and a blood glucose monitoring method.
Background
Blood glucose monitoring is of vital importance for the treatment and management of diabetes. The current blood glucose monitoring modes mainly comprise a traditional blood glucose monitoring mode and a noninvasive Continuous Glucose Monitoring (CGM) mode, wherein the traditional blood glucose monitoring mode, such as fingertip capillary blood glucose monitoring, can provide accurate blood glucose reading, but needs to puncture skin repeatedly to collect blood, so that inconvenience and pain are brought to patients, and compliance of the patients is seriously affected. The noninvasive Continuous Glucose Monitoring (CGM) method can perform blood glucose monitoring on the surface of the skin by gathering skin tissue fluid, and can provide continuous and comprehensive whole-day blood glucose information without puncturing the skin, but the detection method is often polluted by sweat, uric acid and other urinary substances on the surface of the skin, produces interference current and seriously influences the accuracy of blood glucose monitoring.
Disclosure of Invention
An object of the embodiment of the invention is to provide a novel blood glucose monitoring technical scheme.
According to a first aspect of the present invention, there is provided a blood glucose monitoring device comprising a tissue fluid aggregation module, a first sensor, a second sensor, a first voltage detection module, a second voltage detection module, a reference electrode, a control module, wherein;
the tissue fluid aggregation module is connected between the control module and the first sensor and is used for aggregating subcutaneous tissue fluid under the control of the control module;
The first sensor is used for generating electrochemical reaction with the skin surface of subcutaneous tissue fluid gathered by the tissue fluid gathering module to output first current;
The second sensor is connected with the reference electrode and is used for generating electrochemical reaction with the surface of the skin attached to the reference electrode to output second current;
the first voltage detection module is connected between the first sensor and the control module and is used for monitoring a first voltage value of the first current and sending the first voltage value to the control module;
The second voltage detection module is connected between the second sensor and the control module and is used for monitoring a second voltage value of the second current and sending the second voltage value to the control module;
the control module is used for obtaining the blood glucose concentration value according to the first voltage value and the second voltage value.
Optionally, the first voltage detection module and the second voltage detection module are the same, the device further includes a gating module, the first voltage detection module is connected between the control module and the gating module, and the control module is connected with a control end of the gating module, and is used for controlling the gating module to gate the first sensor and the second sensor respectively at different moments.
Optionally, the interstitial fluid accumulation module comprises a boost circuit and an accumulation electrode, the boost circuit is connected between the control module and the first end of the accumulation electrode, the second end of the accumulation electrode is connected with the first sensor, and the accumulation electrode accumulates subcutaneous tissue fluid under the boosting effect of the boost circuit.
Optionally, the apparatus further includes a communication module, where the communication module is connected to the control module, and the communication module is configured to send the first voltage value and the second voltage value to a target device under control of the control module;
The control module is used for receiving the blood glucose concentration value returned by the target device for the first voltage value and the second voltage value through the communication module.
According to a second aspect of the present invention there is provided a blood glucose monitoring method for use with the device of the first aspect, the method comprising:
Under the condition that the tissue fluid aggregation module is controlled to aggregate subcutaneous tissue fluid, a first voltage value detected by the first voltage detection module and a second voltage value detected by the second voltage detection module are obtained;
and determining a blood glucose concentration value according to the first voltage value and the second voltage value.
Optionally, the method further comprises:
under the condition that the tissue fluid aggregation module is not controlled to aggregate subcutaneous tissue fluid, acquiring a third voltage value detected by the first voltage detection module and a fourth voltage value detected by the second voltage detection module;
the determining a blood glucose concentration value from the first voltage value and the second voltage value includes:
and determining the blood glucose concentration value according to the first voltage value, the second voltage value, the third voltage value and the fourth voltage value.
Optionally, the determining the blood glucose concentration value according to the first voltage value, the second voltage value, the third voltage value, and the fourth voltage value includes:
Determining a first current value according to the first voltage value and the third voltage value;
determining a second current value according to the second voltage value and the fourth voltage value;
Determining a target current value according to the first current value and the second current value, wherein the target current value is a current difference value between the first current value and the second current value;
and determining a blood glucose concentration value corresponding to the target current value according to a preset mapping relation and the target current value, wherein the preset mapping relation is a corresponding relation between current and blood glucose concentration.
Optionally, the method further comprises:
Receiving sampling parameters, wherein the sampling parameters comprise sampling starting time and sampling time interval;
determining a plurality of sampling instants in response to the sampling parameters;
under the condition that the sampling starting moment is reached, controlling the tissue fluid aggregation module not to aggregate subcutaneous tissue fluid;
and controlling the tissue fluid aggregation module to aggregate subcutaneous tissue fluid when the sampling starting moment is not reached in the sampling moments.
Optionally, after the controlling the interstitial fluid accumulation module to accumulate subcutaneous tissue fluid, the method further comprises:
And under the condition that the control time length is longer than or equal to the preset time length, executing the step of acquiring the first voltage value monitored by the first voltage detection module and the second voltage value monitored by the second voltage detection module.
Optionally, the first voltage detection module and the second voltage detection module are the same, the device further includes a gating module, the first voltage detection module is connected between the control module and the gating module, the control module is connected with a control end of the gating module, and is used for controlling the gating module to gate the first sensor and the second sensor at different moments respectively, and the method further includes:
and controlling the gating module to sequentially gate the first sensor and the second sensor when any sampling time of the sampling times is reached.
The blood glucose monitoring method has the advantages that the reference electrode and the second sensor are arranged, so that a channel for performing electrochemical reaction on secretion such as sweat and uric acid on the surface of the skin and glucose reaction enzyme on the second sensor can be provided, and the second voltage value corresponding to noise current generated by the electrochemical reaction can be detected through the second voltage detection module, so that correction calculation can be performed on the first voltage value based on the second voltage value corresponding to the noise current in blood glucose monitoring, the influence of secretion substances such as sweat and uric acid on the surface of the skin on the accuracy of blood glucose monitoring is avoided, the accuracy of blood glucose monitoring is improved, and in addition, the blood glucose monitoring method can be realized without penetrating the skin and the compliance of patients is not influenced.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and together with the description, serve to explain the principles of the invention.
FIG. 1 is a schematic diagram of a blood glucose monitoring device according to one embodiment of the present invention;
FIG. 2 is a schematic diagram of a blood glucose monitoring device according to another embodiment of the present invention;
FIG. 3 is a flow chart of a blood glucose monitoring method according to one embodiment of the invention;
fig. 4 is a flow chart of a blood glucose monitoring method according to an example of the invention.
Detailed Description
Various exemplary embodiments of the present invention will now be described in detail with reference to the accompanying drawings. It should be noted that the relative arrangement of the components and steps, numerical expressions and numerical values set forth in these embodiments do not limit the scope of the present invention unless it is specifically stated otherwise.
The following description of at least one exemplary embodiment is merely exemplary in nature and is in no way intended to limit the invention, its application, or uses.
Techniques, methods, and apparatus known to one of ordinary skill in the relevant art may not be discussed in detail, but are intended to be part of the specification where appropriate.
In all examples shown and discussed herein, any specific values should be construed as merely illustrative, and not a limitation. Thus, other examples of exemplary embodiments may have different values.
It should be noted that like reference numerals and letters refer to like items in the following figures, and thus once an item is defined in one figure, no further discussion thereof is necessary in subsequent figures.
Treatment of diabetes requires long-term monitoring of blood glucose levels in order to adjust the treatment regimen to achieve glycemic control goals, reducing the risk of complications. Currently, blood glucose monitoring methods are mainly divided into a traditional blood glucose monitoring method and a noninvasive continuous monitoring glucose monitoring (CGM) method. Among them, the traditional blood glucose monitoring method, such as fingertip capillary blood glucose monitoring, can provide accurate blood glucose readings, but needs to puncture the skin repeatedly to collect blood, which brings inconvenience and pain to the patient and seriously affects the compliance of the patient. Non-invasive Continuous Glucose Monitoring (CGM) methods, such as by blood glucose monitoring of the skin surface after accumulation of skin tissue fluid, do not require skin pricking and are capable of providing continuous, comprehensive, all-day blood glucose information. However, the monitoring mode is often interfered by the secretion substances such as sweat and uric acid on the skin surface, and the secretion substances can react with the glucose sensor electrochemically to generate interference current, so that the accuracy of blood glucose monitoring is seriously affected.
Therefore, how to accurately measure the glucose level in tissue fluid without penetrating the skin while avoiding the influence of the secretion on the skin surface on the blood glucose measurement result is an urgent technical problem to be solved.
For the above technical problems, embodiments of the present disclosure relate to a technical solution of a new blood glucose monitoring device. Fig. 1 illustrates a schematic diagram of a blood glucose monitoring device 100, according to some embodiments. As shown in FIG. 1, the blood glucose monitoring device 100 includes a tissue fluid aggregation module 11, a first sensor 12, a second sensor 13, a first voltage detection module 15, a second voltage detection module 16, a reference electrode 14, and a control module 10.
The control module 10 may be a Microprocessor (Microprocessor), a Digital Signal Processor (DSP), a Programmable Logic Controller (PLC), etc., and those skilled in the art will understand that the specific type of control module is not limited herein.
The first sensor 12 and the second sensor 13 may each be a glucose sensor. The glucose sensor carries a glucose enzyme which can react electrochemically with glucose to produce a reaction current.
The first voltage detection module 15 and the second voltage detection module 16 may be high-precision voltage acquisition modules such as AFE (Analog Front End).
The tissue fluid accumulation module 11 is connected between the control module 10 and the first sensor 12 for accumulating subcutaneous tissue fluid under the control of the control module 10.
Specifically, the skin attaching end of the tissue fluid accumulation module 11 is used for attaching to the skin, the first connecting end of the tissue fluid accumulation module 11 is connected with the first end of the control module 10, and the tissue fluid accumulation module 11 is used for accumulating subcutaneous tissue fluid at the skin attaching end of the tissue fluid accumulation module under the control of the control module 10. The second connection end of the interstitial fluid accumulation module 11 is connected to the first connection end of the first sensor 12. The first sensor 12 is configured to output a first current through an electrochemical reaction with a skin surface of subcutaneous tissue fluid collected by the tissue fluid collection module 11 (i.e., a skin surface to which a skin-attaching end of the tissue fluid collection module 11 is attached).
The second sensor 13 is connected with the reference electrode 14, and the second sensor 13 is used for generating electrochemical reaction with the surface of the skin attached to the reference electrode 14 to output second current.
Specifically, the reference electrode 14 may also be attached to the skin, and the first end of the second sensor 13 is connected to the reference electrode 14, so that the second sensor 13 can perform electrochemical reaction with the sweat, uric acid, and other urinary substances on the surface of the skin to which the reference electrode 14 is attached to output the second current. The second current here may also be referred to as noise current.
The first voltage detection module 15 is connected between the first sensor 12 and the control module 10, and is configured to monitor a first voltage value of the first current and send the first voltage value to the control module 10. The second voltage detection module 16 is connected between the second sensor 13 and the control module 10, and is configured to monitor a second voltage value of the second current and send the second voltage value to the control module 10.
Specifically, one end of the first voltage detection module 15 is connected to the second end of the control module 10, and the other end is connected to the second end of the first sensor 12. One end of the second voltage detection module 16 is connected to the third end of the control module 10, and the other end is connected to the second end of the second sensor 13. When the first current flows through the first voltage detection module 15, the first current may generate a voltage drop through the first voltage detection module 15 due to the large internal resistance of the first voltage detection module 15. The voltage drop can be detected by the first voltage detection module 15 to obtain a first voltage value. Similarly, the second voltage detection module 16 may also detect a voltage drop generated when the second current flows through itself, so as to obtain the second voltage value.
In some embodiments, to avoid affecting the accuracy of blood glucose monitoring due to differences in the types of the first voltage detection module and the second voltage detection module (i.e., differences in internal resistance), the first voltage detection module and the second voltage detection module may be provided as the same type of voltage detection module with the same specification (i.e., voltage detection modules with the same internal resistance).
The control module 10 is used for obtaining the blood glucose concentration value according to the first voltage value and the second voltage value.
For example, the internal resistances of the first voltage detection module and the second voltage detection module are the same, after the control module receives the first voltage value and the second voltage value, the second voltage value is a voltage value corresponding to the noise current (i.e., the second current), so that an actual voltage value can be obtained after the first voltage value and the second voltage value are differenced, then the actual voltage value is determined to be converted into an actual current value according to the internal resistance value of the first voltage detection module or the second voltage detection module, and a blood glucose concentration value corresponding to the actual current value is determined according to the actual current value and a preset corresponding relation between the current and the blood glucose concentration.
According to the embodiment of the application, the reference electrode and the second sensor are arranged, so that a channel for performing electrochemical reaction on secretion such as sweat and uric acid on the surface of the skin and glucose reaction enzyme on the second sensor can be provided, and the second voltage value corresponding to noise current generated by the electrochemical reaction can be detected by the second voltage detection module, so that correction calculation can be performed on the first voltage value based on the second voltage value corresponding to the noise current in blood glucose monitoring, the influence of the secretion such as sweat and uric acid on the surface of the skin on the accuracy of blood glucose monitoring is avoided, the accuracy of blood glucose monitoring is improved, and in addition, the blood glucose monitoring method can be realized without penetrating the skin, and the compliance of a patient is not influenced.
In some embodiments, as shown in fig. 2, the first voltage detection module 15 and the second voltage detection module 16 are the same, that is, there is only one voltage detection module in the blood glucose monitoring device, and the voltage detection module may be the first voltage detection module or the second voltage detection module, which is only taken as an example of the first voltage detection module 15.
The blood glucose monitoring device 100 further comprises a gating module 17, wherein the first voltage detection module 15 is connected between the control module 10 and the gating module 17, and the control module 10 is connected with a control end of the gating module 17 and is used for controlling the gating module 17 to gate the first sensor 12 and the second sensor 13 respectively at different moments.
Specifically, one end of the first voltage detection module 15 is connected to the second end of the control module 10, and the other end is connected to the first connection end of the gating module 17, and the second connection end of the gating module 17 can be switched between the first sensor 12 and the second sensor 13. A third terminal of the control module 10 is connected to a control terminal of the gating module 17, and the control module 10 may control the second connection terminal of the gating module 17 to gate the first sensor 12 and the second sensor 13 at different times, respectively. When the second connection end of the gating module 17 gates the first sensor 12, the voltage value detected by the first voltage detecting module 15 is a first voltage value corresponding to the first current, and when the second connection end of the gating module 17 gates the second sensor 13, the voltage value detected by the first voltage detecting module 15 is a second voltage value corresponding to the second current.
According to the embodiment of the application, the first voltage value and the second voltage value are obtained by arranging the voltage detection module and respectively gating the first sensor and the second sensor through the gating module, so that the hardware quantity of the blood glucose monitoring device can be reduced and the cost can be saved under the condition that the voltage acquisition of the first voltage value and the second voltage value is not influenced.
In some embodiments, tissue fluid collection module 11 includes a boost circuit 111 and a collection electrode 112, boost circuit 111 being connected between control module 10 and a first end of collection electrode 112, a second end of collection electrode 112 being connected to first sensor 12, collection electrode 112 collecting subcutaneous tissue fluid under the boost of boost circuit 111.
In this embodiment, the skin attaching end of the tissue fluid aggregation module 11 is the skin attaching end of the aggregation electrode 112, and is used for attaching to the skin. The first connection end of the tissue fluid accumulation module 11 is connected to the first end of the control module 10, that is, the first connection end of the boost circuit 111 is connected to the first end of the control module 10. The second connection terminal of the voltage boosting circuit 111 is connected to the first terminal of the collecting electrode. The second connection end of the tissue fluid aggregation module 11 is connected to the first connection end of the first sensor 12, that is, the second end of the aggregation electrode 12 is connected to the first connection end of the first sensor 12. The booster circuit 111 is used for boosting the aggregation electrode 112 to form an electric field so as to aggregate subcutaneous tissue fluid of the skin to which the aggregation electrode 112 is attached.
According to the embodiment of the application, the tissue fluid is gathered by forming the electric field at the gathering electrode by the booster circuit, so that subcutaneous tissue fluid can be gathered conveniently, and the booster circuit is easy to control and can be operated conveniently by a user.
In some embodiments, the blood glucose monitoring apparatus 100 further comprises a communication module 18, the communication module 18 being connected to the control module 10, the communication module 18 being configured to send the first voltage value and the second voltage value to the target device under control of the control module 10, the control module 10 being configured to receive the blood glucose concentration value returned by the target device for the first voltage value and the second voltage value via the communication module 18.
In this embodiment, the communication module 18 may be a wireless communication module, for example, a wifi communication module, a bluetooth module, or the like, or may be a wired communication module, for example, a USB communication module, or the like, or may be another communication module.
In the example of a blood glucose monitoring device as shown in fig. 2, the communication module 18 may be connected to a fourth end of the control module 10.
The control module 10 may control the communication module 18 to transmit the first voltage value and the second voltage value to the target device. The target device may be an electronic device, for example, a mobile phone, a computer, or the like, or may be a server, which is not limited herein.
In the case that the target device is an electronic device, the electronic device may also communicate with the server to upload the first voltage value and the second voltage value to the server through the electronic device.
After receiving the first voltage value and the second voltage value, the target device may obtain the blood glucose concentration value according to the first voltage value and the second voltage value. And, the target device may send the returned blood glucose concentration values for the first voltage value and the second voltage value to the control module 10 via the communication module 18.
In some examples, the blood glucose monitoring device further comprises a display module.
In this example, after the control module receives the blood glucose concentration value returned by the target device for the first voltage value and the second voltage value, the control module may further control the display module to display the blood glucose concentration value.
In some examples, the target device may also be connected to a medical platform such as a hospital consultation platform, and when the target device returns a blood glucose concentration value to the control module, the blood glucose concentration value may also be sent to the medical platform so that the medical platform may propose medical advice to the user based on the blood glucose concentration value.
According to the embodiment of the application, the communication module is arranged to upload the first voltage value and the second voltage value to the target equipment, so that the target equipment calculates the blood glucose concentration value, the power consumption of the blood glucose monitoring device can be reduced, and the endurance time can be prolonged.
Fig. 3 shows a blood glucose monitoring method applied to the blood glucose monitoring device shown in fig. 1 or fig. 2, and in particular, may be performed by a control module of the blood glucose monitoring device shown in fig. 1 or fig. 2, wherein the method comprises step S3100 and step S3200.
In step S3100, when the tissue fluid aggregation module 11 is controlled to aggregate subcutaneous tissue fluid, the first voltage value detected by the first voltage detection module 15 and the second voltage value detected by the second voltage detection module 16 are acquired.
In this embodiment, the first voltage detection module and the second voltage detection module may be the same as shown in the description of fig. 2, that is, the first voltage detection module in fig. 2 may be the first voltage detection module or the second voltage detection module. The first voltage detection module and the second voltage detection module may not be the same as shown in fig. 1, and are not limited herein.
When the user attaches the blood glucose monitoring device to the skin, the tissue fluid aggregation module 11 may be controlled to aggregate subcutaneous tissue fluid to obtain the first voltage value and the second voltage value.
It should be understood by those skilled in the art that the specific method for controlling the tissue fluid aggregation module 11 to aggregate the subcutaneous tissue fluid in step S3100 is not limited, that is, the tissue fluid aggregation module 11 may be controlled to aggregate the subcutaneous tissue fluid at a specific time, or the tissue fluid aggregation module 11 may be controlled to aggregate the subcutaneous tissue fluid when an aggregation command is received, or other control manners are not limited herein.
Step S3200, determining the blood glucose concentration value according to the first voltage value and the second voltage value.
For example, after the first voltage detection module and the second voltage detection module have the same internal resistance, the control module obtains the first voltage value and the second voltage value, and then, the second voltage value is a voltage value corresponding to the noise current (i.e., the second current), so that an actual voltage value can be obtained after the first voltage value and the second voltage value are differenced, then, the actual voltage value is determined to be converted into an actual current value according to the internal resistance value of the first voltage detection module or the second voltage detection module, and a blood glucose concentration value corresponding to the actual current value is determined according to the corresponding relation between the actual current value and a preset current and a blood glucose concentration.
According to the embodiment of the present application, by acquiring the first voltage value detected by the first voltage detection module 15 and the second voltage value detected by the second voltage detection module 16 in the case of controlling the interstitial fluid aggregation module 11 to aggregate subcutaneous tissue fluid, the blood glucose concentration value is determined from the first voltage value and the second voltage value. The method can be used for introducing the second voltage value generated by the participation of the sweat, uric acid and other secretion substances on the surface of the skin in the electrochemical reaction into the calculation process of the blood sugar concentration value so as to correct the first voltage value, thereby avoiding the influence of the sweat, uric acid and other secretion substances on the surface of the skin on the accuracy of blood sugar monitoring, improving the accuracy of blood sugar monitoring, and in addition, the blood sugar monitoring method can be realized without penetrating the skin and does not influence the compliance of patients.
In theory, in the case that the tissue fluid aggregation module is not controlled to aggregate the subcutaneous tissue fluid, the third voltage value detected by the first voltage detection module and the fourth voltage value detected by the second voltage detection module should be the same. However, since the blood glucose monitoring device 100 includes the first sensor and the second sensor, both sensors are glucose sensors, but the two sensors may be almost identical, that is, the first sensor and the second sensor may react with glucose to different extents, and the third voltage value and the fourth voltage value measured correspondingly may also be different, and if the calculation of the blood glucose concentration value is directly performed by the first voltage value and the second voltage value, there is a problem that the blood glucose monitoring is inaccurate due to the hardware difference between the first sensor and the second sensor. To address this issue, in some embodiments, the method further includes step S4100.
In step S4100, in a case where the tissue fluid aggregation module 11 is not controlled to aggregate the subcutaneous tissue fluid, the third voltage value detected by the first voltage detection module 15 and the fourth voltage value detected by the second voltage detection module 16 are acquired.
In this embodiment, the third voltage value is the voltage error value of the first sensor, and the fourth voltage value is the voltage error value of the second sensor.
In these embodiments, determining the blood glucose concentration value from the first voltage value and the second voltage value in step S3200 includes step S4200.
Step S4200, determining the blood glucose concentration value according to the first voltage value, the second voltage value, the third voltage value, and the fourth voltage value.
For example, the first voltage value may be subtracted from the third voltage value to obtain a first actual voltage value, the second voltage value may be subtracted from the fourth voltage value to obtain a second actual voltage value, and then the first actual voltage value may be subtracted from the second actual voltage value to obtain a denoised voltage value. And dividing the denoised voltage value by the internal resistance value of the voltage detection module to obtain a denoised current value. And determining a corresponding blood glucose concentration value according to the denoised current value.
In some embodiments, the determining the blood glucose concentration value in step S4200 according to the first voltage value, the second voltage value, the third voltage value, and the fourth voltage value includes steps S4200.1-S4200.4.
Step S4200.1, determining a first current value according to the first voltage value and the third voltage value.
In this embodiment, the first actual voltage value is determined according to the voltage difference between the first voltage value and the third voltage value. And dividing the first actual voltage value by the internal resistance value of the first voltage detection module to obtain a first current value.
And step S4200.2, determining a second current value according to the second voltage value and the fourth voltage value.
In this embodiment, the second actual voltage value is determined according to the voltage difference between the second voltage value and the fourth voltage value. And dividing the second actual voltage value by the internal resistance value of the second voltage detection module to obtain a second current value.
And step S4200.3, determining a target current value according to the first current value and the second current value.
In this embodiment, the target current value is a current difference between the first current value and the second current value.
Step S4200.4, determining a blood glucose concentration value corresponding to the target current value according to a preset mapping relation and the target current value.
In this embodiment, the preset mapping relationship is a correspondence relationship between the current and the blood glucose concentration. That is, one blood glucose concentration value corresponds to one current value.
In some embodiments, the method further comprises steps S5100-S5400.
In step S5100, sampling parameters are received.
In this embodiment, the sampling parameters include a sampling start time and a sampling time interval.
In some examples, the sampling parameter is a control module that is sent to the blood glucose monitoring device by a target device, such as an electronic device.
In other examples, the blood glucose monitoring device includes an input module for a user to input a sampling parameter to input the sampling parameter.
In step S5200, a plurality of sampling instants are determined in response to the sampling parameters.
Illustratively, the sampling start time is 0:00 and the sampling time interval is 1h, then the plurality of sampling times is 0:00, 1:00, 2:00, 3:00..23:00, 0:00.
In step S5300, when the sampling start time is reached, the tissue fluid accumulation module 11 is controlled not to accumulate subcutaneous tissue fluid.
Continuing with the example above, the sampling start time is 0:00, and when the current time reaches 0:00, the tissue fluid accumulation module is controlled not to accumulate subcutaneous tissue fluid.
In the above-described embodiment, in which the corresponding interstitial fluid accumulation module includes a boost circuit and an accumulation electrode, the control interstitial fluid accumulation module does not accumulate subcutaneous tissue fluid, comprising:
And controlling the boosting circuit not to boost the collecting electrode.
In step S5400, when a non-sampling start time out of the plurality of sampling times is reached, the tissue fluid accumulation module 11 is controlled to accumulate subcutaneous tissue fluid.
Continuing with the above example, where the sampling start time is 0:00 and the sampling time interval is 1h, the plurality of sampling times are 0:00, 1:00, 2:00, 3:00..23:00, 0:00. And when the current time reaches the non-sampling starting time of 1:00, 2:00 and the like, controlling the tissue fluid aggregation module to aggregate the subcutaneous tissue fluid.
In the above embodiment, where the corresponding interstitial fluid aggregation module includes a boost circuit and an aggregation electrode, the controlling the interstitial fluid aggregation module to aggregate subcutaneous tissue fluid includes:
And controlling the boosting circuit to boost the aggregation electrode.
In order to avoid the problem that the accuracy of blood glucose monitoring is reduced due to the fact that the amount of the accumulated subcutaneous tissue fluid is small as the period of time for which the tissue fluid accumulation module accumulates the subcutaneous tissue fluid is short, the theoretical period of time for which the tissue fluid is accumulated, namely the preset period of time, is set according to experimental experience, and when the control period of time for which the tissue fluid accumulation module accumulates the subcutaneous tissue fluid reaches the preset period of time, the first voltage value and the second voltage value are detected.
Based on this, in some embodiments, after controlling the interstitial fluid accumulation module to accumulate subcutaneous tissue fluid in step S3100 or step S5400, the method further comprises:
And under the condition that the control time length is longer than or equal to the preset time length, executing the step of acquiring the first voltage value monitored by the first voltage detection module and the second voltage value monitored by the second voltage detection module.
In this embodiment, the preset time period may be a time period required for the corresponding tissue fluid aggregation module to aggregate the subcutaneous tissue fluid under the condition that the first voltage value tends to be stable in the historical tissue fluid aggregation process.
In the above embodiment where the controlling the tissue fluid aggregation module to aggregate subcutaneous tissue fluid includes controlling the boosting circuit to boost the aggregation electrode, the control duration may be a duration during which the boosting circuit boosts the aggregation electrode.
In the above embodiment, where the first voltage detection module and the second voltage detection module are the same, the blood glucose monitoring device further includes a gating module, the method further includes:
In the case where any one of the plurality of sampling timings is reached, the control gating module sequentially gates the first sensor 12 and the second sensor 13.
Continuing with the above example, the plurality of sampling moments are 0:00, 1:00, 2:00, 3:00..23:00, 0:00, and when the current moment reaches the initial sampling moment 0:00, the first sensor and the second sensor are sequentially gated by the gating module, so that a third voltage value and a fourth voltage value can be obtained. When the current time reaches 1:00, the first sensor and the second sensor are sequentially gated by the gating module, so that a first voltage value and a second voltage value can be obtained.
In some embodiments, to reduce the power consumption of the blood glucose monitoring device, the first sensor and the second sensor are controlled to react electrochemically with the skin, respectively, in case any one of a plurality of sampling instants is reached.
In this embodiment, the glucose reaction enzymes on the first sensor and the second sensor may be activated to electrochemically react with the skin by issuing a trigger command to the first sensor and the second sensor.
As shown in fig. 4, a blood glucose monitoring method according to one example of the application is shown. The method is executed by a control module of the blood glucose monitoring device and comprises the steps S1-S13.
Step S1, receiving sampling parameters sent by electronic equipment.
In this example, the sampling parameters include a sampling start time and a sampling time interval.
In other examples, user-entered sampling parameters may also be received.
Step S2, a plurality of sampling moments are determined in response to the sampling parameters.
Illustratively, the sampling start time is 0:00 and the sampling time interval is 1h, then the plurality of sampling times is 0:00, 1:00, 2:00, 3:00..23:00, 0:00.
Step S3, if the current time reaches the sampling start time, executing step S4, and if not, returning to step S3.
And S4, respectively sending a trigger instruction to the first sensor and the second sensor to trigger the electrochemical reaction.
In this example, triggering the first sensor to electrochemically react with the skin produces a reverse current, and triggering the second sensor to electrochemically react with the skin produces a reverse current.
And S5, gating the first sensor to acquire a third voltage value detected by the first voltage detection module.
In this example, the third voltage value is a voltage value corresponding to a reverse current generated by the electrochemical reaction between the first sensor and the skin.
And S6, gating the second sensor to acquire a fourth voltage value detected by the first voltage detection module.
In this example, the fourth voltage value is a voltage value corresponding to a reverse current generated by the electrochemical reaction between the second sensor and the skin.
Step S7, judging whether the current time reaches the non-sampling starting time in the sampling times, if yes, executing step S8, otherwise, returning to step S7.
And S8, controlling a boosting circuit to boost the aggregation electrode, and respectively sending trigger instructions to the first sensor and the second sensor to trigger the electrochemical reaction.
The triggering of the electrochemical reaction in this step is substantially the same as in step S4, and will not be described here again.
Step S9, whether the control duration is greater than or equal to the preset duration or not is judged, if yes, step S10 is executed, and if not, step S8 is returned to.
Step S10, a first sensor is gated, and a first voltage value detected by a first voltage detection module is obtained.
Step S11, a second sensor is gated, and a second voltage value detected by the first voltage detection module is obtained.
Step S12, the first voltage value, the second voltage value, the third voltage value and the fourth voltage value are sent to the server through the electronic equipment.
In this example, the server calculates the blood glucose concentration value according to the first voltage value, the second voltage value, the third voltage value, and the fourth voltage value, to obtain the corresponding blood glucose concentration value. The manner in which the server calculates the blood glucose concentration value is the same as the manner in which the control module calculates the blood glucose concentration value, and will not be described here again.
Step S13, the receiving server returns the blood sugar concentration value based on the first voltage value, the second voltage value, the third voltage value and the fourth voltage value.
The present invention may be a system, method, and/or computer program product. The computer program product may include a computer readable storage medium having computer readable program instructions embodied thereon for causing a processor to implement aspects of the present invention.
The computer readable storage medium may be a tangible device that can hold and store instructions for use by an instruction execution device. The computer readable storage medium may be, for example, but not limited to, an electronic storage device, a magnetic storage device, an optical storage device, an electromagnetic storage device, a semiconductor storage device, or any suitable combination of the foregoing. More specific examples (a non-exhaustive list) of the computer-readable storage medium include a portable computer diskette, a hard disk, a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), a Static Random Access Memory (SRAM), a portable compact disc read-only memory (CD-ROM), a Digital Versatile Disc (DVD), a memory stick, a floppy disk, a mechanical encoding device, punch cards or intra-groove protrusion structures such as those having instructions stored thereon, and any suitable combination of the foregoing. Computer-readable storage media, as used herein, are not to be construed as transitory signals per se, such as radio waves or other freely propagating electromagnetic waves, electromagnetic waves propagating through waveguides or other transmission media (e.g., optical pulses through fiber optic cables), or electrical signals transmitted through wires.
The computer readable program instructions described herein may be downloaded from a computer readable storage medium to a respective computing/processing device or to an external computer or external storage device over a network, such as the internet, a local area network, a wide area network, and/or a wireless network. The network may include copper transmission cables, fiber optic transmissions, wireless transmissions, routers, firewalls, switches, gateway computers and/or edge servers. The network interface card or network interface in each computing/processing device receives computer readable program instructions from the network and forwards the computer readable program instructions for storage in a computer readable storage medium in the respective computing/processing device.
Computer program instructions for carrying out operations of the present invention may be assembly instructions, instruction Set Architecture (ISA) instructions, machine-related instructions, microcode, firmware instructions, state setting data, or source or object code written in any combination of one or more programming languages, including an object oriented programming language such as SMALLTALK, C ++ or the like and conventional procedural programming languages, such as the "C" programming language or similar programming languages. The computer readable program instructions may be executed entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server. In the case of a remote computer, the remote computer may be connected to the user's computer through any kind of network, including a Local Area Network (LAN) or a Wide Area Network (WAN), or may be connected to an external computer (for example, through the Internet using an Internet service provider). In some embodiments, aspects of the present invention are implemented by personalizing electronic circuitry, such as programmable logic circuitry, field Programmable Gate Arrays (FPGAs), or Programmable Logic Arrays (PLAs), with state information for computer readable program instructions, which can execute the computer readable program instructions.
Various aspects of the present invention are described herein with reference to flowchart illustrations and/or block diagrams of methods, apparatus (systems) and computer program products according to embodiments of the invention. It will be understood that each block of the flowchart illustrations and/or block diagrams, and combinations of blocks in the flowchart illustrations and/or block diagrams, can be implemented by computer-readable program instructions.
These computer readable program instructions may be provided to a processor of a general purpose computer, special purpose computer, or other programmable data processing apparatus to produce a machine, such that the instructions, which execute via the processor of the computer or other programmable data processing apparatus, create means for implementing the functions/acts specified in the flowchart and/or block diagram block or blocks. These computer readable program instructions may also be stored in a computer readable storage medium that can direct a computer, programmable data processing apparatus, and/or other devices to function in a particular manner, such that the computer readable medium having the instructions stored therein includes an article of manufacture including instructions which implement the function/act specified in the flowchart and/or block diagram block or blocks.
The computer readable program instructions may also be loaded onto a computer, other programmable data processing apparatus, or other devices to cause a series of operational steps to be performed on the computer, other programmable apparatus or other devices to produce a computer implemented process such that the instructions which execute on the computer, other programmable apparatus or other devices implement the functions/acts specified in the flowchart and/or block diagram block or blocks.
The flowcharts and block diagrams in the figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods and computer program products according to various embodiments of the present invention. In this regard, each block in the flowchart or block diagrams may represent a module, segment, or portion of instructions, which comprises one or more executable instructions for implementing the specified logical function(s). In some alternative implementations, the functions noted in the block may occur out of the order noted in the figures. For example, two blocks shown in succession may, in fact, be executed substantially concurrently, or the blocks may sometimes be executed in the reverse order, depending upon the functionality involved. It will also be noted that each block of the block diagrams and/or flowchart illustration, and combinations of blocks in the block diagrams and/or flowchart illustration, can be implemented by special purpose hardware-based systems which perform the specified functions or acts, or combinations of special purpose hardware and computer instructions. It is well known to those skilled in the art that implementation by hardware, implementation by software, and implementation by a combination of software and hardware are all equivalent.
The foregoing description of embodiments of the invention has been presented for purposes of illustration and description, and is not intended to be exhaustive or limited to the embodiments disclosed. Many modifications and variations will be apparent to those of ordinary skill in the art without departing from the scope and spirit of the various embodiments described. The terminology used herein was chosen in order to best explain the principles of the embodiments, the practical application, or the technical improvements in the marketplace, or to enable others of ordinary skill in the art to understand the embodiments disclosed herein. The scope of the invention is defined by the appended claims.
Claims (9)
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202411874132.7A CN119770035B (en) | 2024-12-18 | 2024-12-18 | Blood glucose monitoring devices and methods |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202411874132.7A CN119770035B (en) | 2024-12-18 | 2024-12-18 | Blood glucose monitoring devices and methods |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN119770035A CN119770035A (en) | 2025-04-08 |
| CN119770035B true CN119770035B (en) | 2025-11-04 |
Family
ID=95243221
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202411874132.7A Active CN119770035B (en) | 2024-12-18 | 2024-12-18 | Blood glucose monitoring devices and methods |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN119770035B (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN120406632B (en) * | 2025-07-03 | 2025-09-12 | 歌尔股份有限公司 | Continuous blood glucose monitoring equipment control method, device and equipment |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2822519Y (en) * | 2005-08-18 | 2006-10-04 | 圣美迪诺医疗科技(湖州)有限公司 | Dynamic glucose sensing monitoring circuit |
| CN101214152A (en) * | 2008-01-22 | 2008-07-09 | 天津市先石光学技术有限公司 | Method for micro-wounded dynamically and continuously detecting blood sugar concentration of human body |
Family Cites Families (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6998247B2 (en) * | 2002-03-08 | 2006-02-14 | Sensys Medical, Inc. | Method and apparatus using alternative site glucose determinations to calibrate and maintain noninvasive and implantable analyzers |
| WO2016090189A1 (en) * | 2014-12-03 | 2016-06-09 | The Regents Of The University Of California | Non-invasive and wearable chemical sensors and biosensors |
| CN105615897B (en) * | 2016-04-05 | 2018-12-18 | 京东方科技集团股份有限公司 | A kind of blood sugar monitor and its monitoring method |
| AU2018319524B2 (en) * | 2017-08-21 | 2024-06-13 | Dexcom, Inc. | Continuous glucose monitors and related sensors utilizing mixed model and bayesian calibration algorithms |
| US11559230B2 (en) * | 2018-01-23 | 2023-01-24 | Dexcom, Inc. | Systems, devices, and methods to compensate for temperature effects on sensors |
| JP2019132733A (en) * | 2018-01-31 | 2019-08-08 | シスメックス株式会社 | Apparatus and method for measuring in-vivo component |
| CN109549627A (en) * | 2018-11-23 | 2019-04-02 | 苏州麦米医疗科技有限公司 | A kind of wearable physiological compensation effects equipment of pilot |
| CN115844394A (en) * | 2023-01-09 | 2023-03-28 | 哈尔滨工业大学 | Noninvasive blood glucose detection and regulation system and method based on polymer microneedle array |
| CN118476808A (en) * | 2024-07-15 | 2024-08-13 | 歌尔股份有限公司 | Wearable blood glucose monitoring device |
-
2024
- 2024-12-18 CN CN202411874132.7A patent/CN119770035B/en active Active
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2822519Y (en) * | 2005-08-18 | 2006-10-04 | 圣美迪诺医疗科技(湖州)有限公司 | Dynamic glucose sensing monitoring circuit |
| CN101214152A (en) * | 2008-01-22 | 2008-07-09 | 天津市先石光学技术有限公司 | Method for micro-wounded dynamically and continuously detecting blood sugar concentration of human body |
Also Published As
| Publication number | Publication date |
|---|---|
| CN119770035A (en) | 2025-04-08 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US11864894B2 (en) | Method and system for providing calibration of an analyte sensor in an analyte monitoring system | |
| US20220330856A1 (en) | Analyte monitoring devices and methods | |
| US10342469B2 (en) | Method and system for dynamically updating calibration parameters for an analyte sensor | |
| CA2882514C (en) | Real-time self-calibrating sensor system and method | |
| JP7113833B2 (en) | Computer-implemented methods and portable devices, and computer program products for analyzing glucose monitoring data indicative of glucose levels in bodily fluids | |
| US20150230741A1 (en) | Assessing Measures of Glycemic Variability | |
| JP2002541883A (en) | Glucose monitor calibration method | |
| CN119770035B (en) | Blood glucose monitoring devices and methods | |
| JP2014506676A (en) | Capacitance detection in electrochemical analysis with improved response | |
| KR101440735B1 (en) | Glucose Measurement System Minimize the Number of Blood Sampling and Method Thereof | |
| JP2022542811A (en) | Method for stabilizing continuous blood glucose measurement system | |
| EP3169233A1 (en) | A method and a device for determining a body fluid glucose level of a patient, and a computer program product | |
| CN119632556B (en) | Data processing methods and detection systems, electronic devices and storage media | |
| EP3050504A1 (en) | Continuous glucose monitoring system and monitoring terminal | |
| CN201788165U (en) | Portable intelligent blood glucose meter | |
| CA3039212C (en) | Method for emphasizing analyte values during a therapeutic window | |
| CN115708677A (en) | Data processing method and device, electronic equipment and storage medium | |
| CN115862854A (en) | Method, server and equipment for generating information for blood glucose control |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |