CN112827061A

CN112827061A - Drug release control device, control method thereof, and computer-readable storage medium

Info

Publication number: CN112827061A
Application number: CN202110216039.7A
Authority: CN
Inventors: 谢曦; 王浩; 张涛; 黎洪波; 杨成; 李湘凌; 刘繁茂; 何根; 杭天; 陈惠琄; 夏文豪; 王自鑫; 胡宁
Original assignee: Sun Yat Sen University
Current assignee: Sun Yat Sen University
Priority date: 2021-02-26
Filing date: 2021-02-26
Publication date: 2021-05-25

Abstract

The present application relates to a drug release control device, a control method thereof, a control device, and a storage medium. The drug release control device includes: a blood pressure monitoring device and an ion electrophoresis administration device; the blood pressure monitoring device includes: a physiological signal sensor for acquiring a physiological electrical signal; the control circuit is connected with the physiological signal sensor and used for processing the physiological electric signal to obtain a blood pressure value, determining a blood pressure range to which the blood pressure value belongs, generating a control instruction containing the release start or stop of the drug, and sending the control instruction to the ion electrophoresis dosing device; the ion electrophoresis drug delivery device is used for controlling the drug to start releasing or stop releasing according to the control instruction. The scheme realizes timely release or stop release of the medicine, and achieves the purpose of accurately controlling medicine supply.

Description

Drug release control device, control method thereof, and computer-readable storage medium

Technical Field

The present application relates to the field of medical devices, and in particular, to a drug release control device, a control method thereof, and a computer-readable storage medium.

Background

Cardiovascular disease is one of the most common diseases in humans, and hypertension is the most risk factor in cardiovascular disease. The hypertension emergency patient has the serious consequences of arterial dissection, cerebral hemorrhage and the like due to the sudden rise of blood pressure in a short time under the internal or environmental inducement, thereby threatening the life safety. Clinical intervention and control is complicated and difficult due to the paroxysmal nature of the onset of acute hypertension. At present, the measurement of the blood pressure and the dynamic blood pressure in a conventional clinic diagnosis room is realized by cuff pressurization, the blood pressure can not be monitored in real time for a long time, and the requirements of accurate diagnosis and real-time monitoring on hypertension emergency are difficult to meet. At present, the main administration mode of clinical hypertensive emergency is sublingual buccal administration or intravenous injection, however, when the hypertensive emergency is in rapid attack, patients are often accompanied with acute symptoms such as nausea, vomiting, visual disturbance, severe headache and the like, the normal action ability is greatly interfered, and the sublingual buccal administration or the intravenous injection mode is difficult to guarantee to carry out emergency treatment. The current blood pressure detection and drug administration modes have the problems of low blood pressure monitoring precision or inaccurate administration dose control.

Disclosure of Invention

In view of the above, it is necessary to provide a drug release control device, a control method thereof and a computer readable storage medium capable of controlling drug release in real time and accurately.

A drug release control device comprises a blood pressure monitoring device and an ion electrophoresis administration device;

the blood pressure monitoring device includes:

a physiological signal sensor for acquiring a physiological electrical signal;

the control circuit is connected with the physiological signal sensor and used for processing the physiological electric signal to obtain a blood pressure value, determining a blood pressure range to which the blood pressure value belongs, generating a control instruction containing the release start or stop of the drug, and sending the control instruction to the ion electrophoresis dosing device;

the ion electrophoresis drug delivery device is used for controlling the drug to start releasing or stop releasing according to the control instruction.

In one embodiment, the control circuit includes:

the signal conditioning circuit is connected with the physiological signal sensor and used for amplifying, filtering and voltage-lifting the physiological electric signal and then sending the physiological electric signal to the signal processor;

and the signal processor is connected with the signal conditioning circuit and used for receiving the physiological electric signal processed by the signal conditioning circuit, carrying out signal modulation and digital-to-analog conversion, acquiring a blood pressure value corresponding to the physiological electric signal, determining a blood pressure range to which the blood pressure value belongs, generating a control instruction containing the start release or stop release of the medicine, and sending the control instruction to the ion electrophoresis dosing device.

In one embodiment, the physiological signal sensor comprises:

the pulse sensor is used for monitoring and acquiring a pulse electric signal and comprises one or more of a stress sensor and a photoelectric sensor;

the electrocardio sensor is used for monitoring and acquiring electrocardiosignals and comprises three electrodes;

the signal conditioning circuit includes:

the pulse signal conditioning circuit is respectively connected with the pulse sensor and the signal processor, and comprises a primary amplifying circuit, a band-pass filter, a power frequency wave limiter, a secondary amplifying circuit and a voltage adding circuit, wherein the input end of the primary amplifying circuit is connected with the pulse sensor, the input end of the band-pass filter is connected with the output end of the primary amplifying circuit, the input end of the power frequency wave limiter is connected with the output end of the band-pass filter, the input end of the secondary amplifying circuit is connected with the output end of the power frequency wave limiter, the input end of the voltage adding circuit is connected with the output end of the secondary amplifying circuit, and the output end of the voltage adding circuit is connected with the signal processor;

electrocardiosignal conditioning circuit, respectively with electrocardio sensor and signal processor connect, electrocardiosignal conditioning circuit includes difference amplifier circuit, band pass filter, power frequency wave limiter, second grade amplifier circuit and voltage addition circuit, difference amplifier circuit's input with electrocardio sensor links to each other, band pass filter's input with difference amplifier circuit's output links to each other, power frequency wave limiter's input with band pass filter's output links to each other, second grade amplifier circuit's input with power frequency wave limiter's output links to each other, voltage addition circuit's input with second grade amplifier circuit's output links to each other, voltage addition circuit's output with signal processor links to each other.

In one embodiment, the signal processor is configured to perform digital filtering on the acquired pulse electrical signal and the acquired electrocardiographic signal, extract peaks of the pulse electrical signal and the electrocardiographic signal, obtain pulse transmission time PTT by subtracting a time coordinate of the peak of the electrocardiographic signal from a time coordinate of the peak of the pulse electrical signal, obtain a heart rate according to the pulse transmission time PTT, obtain a time period of the electrocardiographic pulse according to the heart rate, set a threshold range according to the time period, if the pulse transmission time PTT is within the range, retain the threshold range, otherwise, reject a singular value regarded as PTT, and calculate a blood pressure value:

DBP＝(SBP_0)/3+(2DBP_0)/3+Aln((PTT_0)/PTT)-((SBP_0-DBP_0))/3(PTT_0^2)/(PTT^2)

SBP＝DBP+(SBP_0-DBP_0)(PTT_0^2)/(PTT^2)

the blood pressure value comprises a diastolic pressure DBP and a systolic pressure SBP, PTT is the pulse transmission time, DBP _0 is a preset calibration value of the diastolic pressure, SBP _0 is a preset calibration value of the systolic pressure, and PTT _0 is a preset calibration value of the pulse transmission time.

In one embodiment, the blood pressure range includes a first range and a second range, and the control instructions include first instructions and second instructions to:

the signal processor is further configured to determine a blood pressure value corresponding to the acquired physiological electrical signal, determine that the blood pressure value is in a first range if the blood pressure value is higher than a blood pressure threshold, and determine that the blood pressure value is in a second range if the blood pressure value is not greater than the blood pressure threshold;

if the blood pressure value is in a first range, the signal processor generates a first instruction;

and if the blood pressure value is in a second range, the signal processor generates a second instruction.

In one embodiment, the control circuit further comprises:

the data transmission module is connected with the signal processor and is used for transmitting the acquired physiological electric signal and the acquired blood pressure value to the mobile equipment, receiving a control instruction generated by the mobile equipment according to the physiological electric signal and the blood pressure value and sending the control instruction to the ion electrophoresis dosing device;

and the power supply module is used for supplying power to the signal conditioning circuit and the signal processor.

In one embodiment, an ionophoretic drug delivery device comprises:

the ion electrophoresis administration circuit is connected with the control circuit and used for receiving the control instruction and controlling the ion electrophoresis administration device to release the medicine or stop releasing the medicine;

the ion electrophoresis administration device is connected with the ion electrophoresis administration circuit, and can contain medicines inside.

A drug release control method comprising:

acquiring a physiological electrical signal;

processing the physiological electric signal to obtain a blood pressure value, determining a blood pressure range to which the blood pressure value belongs, and generating a control instruction containing the drug start release or the drug stop release;

and controlling the drug to start releasing or stop releasing according to the control instruction.

In one embodiment, the physiological electrical signals include pulse electrical signals and electrocardio signals, digital filtering is performed on the acquired pulse electrical signals and electrocardio signals, peak values are respectively extracted from the pulse electrical signals and the electrocardio signals, the time coordinate of the peak value of the pulse electrical signals is subtracted from the time coordinate of the peak value of the electrocardio signals to obtain pulse transmission time PTT, heart rate is obtained according to the pulse transmission time PTT, the time period of the electrocardio pulses is obtained according to the heart rate, a threshold range is set according to the time period, if the pulse transmission time PTT is in the range, the pulse transmission time PTT is reserved, otherwise, singular values regarded as PTT are removed, and a blood pressure value is calculated:

DBP＝(SBP_0)/3+(2DBP_0)/3+Aln((PTT_0)/PTT)-((SBP_0-DBP_0))/3(PTT_0^2)/(PTT^2)

SBP＝DBP+(SBP_0-DBP_0)(PTT_0^2)/(PTT^2)

A computer-readable storage medium, on which a computer program is stored which, when executed by a processor, carries out the steps of:

acquiring a physiological electrical signal;

According to the drug release control device, the control method and the computer readable storage medium, after the physiological electric signal is obtained, the physiological electric signal is processed to obtain the blood pressure value, then the blood pressure range where the blood pressure value is located is determined, the corresponding control instruction for releasing or stopping releasing the drug is generated according to the determined blood pressure range, the control instruction is sent to the ion electrophoresis drug delivery device, the ion electrophoresis drug delivery device controls the drug to start releasing or stop releasing, the drug is released or stopped releasing in time, and the purpose of accurately controlling the drug supply is achieved.

Drawings

In order to more clearly illustrate the technical solutions in the embodiments or the conventional technologies of the present application, the drawings used in the descriptions of the embodiments or the conventional technologies will be briefly introduced below, it is obvious that the drawings in the following descriptions are only some embodiments of the present application, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.

FIG. 1 is a schematic diagram of the construction of a drug release control device according to one embodiment;

FIG. 2 is a circuit schematic of an STM32 signal processor in one embodiment;

FIG. 3 is a schematic circuit diagram of a power module in one embodiment;

FIG. 4 is a schematic circuit diagram of a serial port module in an embodiment;

FIG. 5 is a circuit diagram of a Bluetooth module in one embodiment;

FIG. 6 is a schematic circuit diagram of an ion phoretic dosing circuit in one embodiment;

FIG. 7 is a schematic electrical diagram of an electrical signal conditioning circuit for an embodiment;

FIG. 8 is a circuit diagram of a pulse signal conditioning circuit according to an embodiment;

FIG. 9 is a schematic flow chart illustrating the control of drug delivery based on physiological electrical signals in one embodiment;

fig. 10 is a schematic flow chart of a drug release control method according to an embodiment.

Description of reference numerals:

description of reference numerals: 100-physiological signal sensor, 110-pulse sensor, 120-electrocardio sensor, 200-control circuit, 210-pulse signal conditioning circuit, 220-electrocardio signal conditioning circuit, 230-signal processor, 240-serial port module, 250-Bluetooth module, 260-power module, 300-ion electrophoresis administration device, 400-PC terminal and 500-mobile phone terminal.

Detailed Description

To facilitate an understanding of the present application, the present application will now be described more fully with reference to the accompanying drawings. Embodiments of the present application are set forth in the accompanying drawings. This application may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete.

Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein in the description of the present application is for the purpose of describing particular embodiments only and is not intended to be limiting of the application.

It will be understood that, as used herein, the terms "first," "second," and the like may be used herein to describe various elements, but these elements are not limited by these terms. These terms are only used to distinguish one element from another.

Spatial relational terms, such as "under," "below," "under," "over," and the like may be used herein to describe one element or feature's relationship to another element or feature as illustrated in the figures. It will be understood that the spatially relative terms are intended to encompass different orientations of the device in use or operation in addition to the orientation depicted in the figures. For example, if the device in the figures is turned over, elements or features described as "below" or "beneath" other elements or features would then be oriented "above" the other elements or features. Thus, the exemplary terms "under" and "under" can encompass both an orientation of above and below. In addition, the device may also include additional orientations (e.g., rotated 90 degrees or other orientations) and the spatial descriptors used herein interpreted accordingly.

It will be understood that when an element is referred to as being "connected" to another element, it can be directly connected to the other element or be connected to the other element through intervening elements. Further, "connection" in the following embodiments is understood to mean "electrical connection", "communication connection", or the like, if there is a transfer of electrical signals or data between the connected objects.

As used herein, the singular forms "a", "an" and "the" may include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms "comprises/comprising," "includes" or "including," etc., specify the presence of stated features, integers, steps, operations, components, parts, or combinations thereof, but do not preclude the presence or addition of one or more other features, integers, steps, operations, components, parts, or combinations thereof. Also, as used in this specification, the term "and/or" includes any and all combinations of the associated listed items.

In one embodiment, as shown in fig. 1, a drug release control device is provided, comprising a blood pressure monitoring device and an iontophoretic drug delivery device 300;

the blood pressure monitoring device includes:

the physiological signal sensor 100 is used for acquiring a physiological electrical signal, which is an electrical signal related to a physiological parameter of a human body, for example, the physiological electrical signal may include a pulse electrical signal, an electrocardiograph signal, and the like, and the physiological signal sensor may include a pulse sensor 110, an electrocardiograph sensor 120, and the like.

The control circuit 200 is connected with the physiological signal sensor and used for processing the physiological electric signal to obtain a blood pressure value, determining a blood pressure range to which the blood pressure value belongs, generating a control instruction containing the release start or stop of the drug, and sending the control instruction to the ion electrophoresis drug delivery device;

the iontophoretic drug delivery device 300 is used to control the drug to be released or to be released in accordance with control instructions.

In the embodiment, the blood pressure can be accurately regulated, the pulse transmission time is calculated through the electrocardio and the pulse, the blood pressure is accurately calculated by taking the pulse transmission time as a parameter, and the blood pressure is regulated and controlled in real time in an automatic drug release mode, so that the blood pressure is kept in a safe range, and the automatic drug release and the real-time regulation and control of the blood pressure are realized.

In one embodiment, the pulse sensor 110 is used to monitor and acquire pulse electrical signals. The pulse sensor adopts multi-sensor selection, and a piezoresistive sensor and a photoelectric sensor can be selected. The piezoresistive sensor is a sensor manufactured by using piezoresistive effect of monocrystalline silicon material and integrated circuit technology, and the change of surface pressure and the change of resistance of the piezoresistive sensor are in a linear relation in a certain interval. The piezoresistive sensor is tightly attached to the skin, deformation of the skin caused by pulse can be detected, the piezoresistive sensor converts the deformation into change of resistance, the designed circuit converts the change of the resistance into the change of voltage, and the voltage signal is amplified and filtered to obtain pulse waves. The photoelectric sensor uses infrared geminate transistors with the wavelength of 850nm, blood oxygen protein in blood pressure has strong reflecting capacity to infrared light, the concentration of the blood oxygen protein in the blood is increased when pulse signals pass through blood vessels, the reflecting capacity to the infrared light is enhanced, the change of light intensity received by the infrared receiving tube can cause the change of voltage at two ends of the receiving tube, and the voltage is amplified and filtered to obtain the pulse waves.

In one embodiment, the cardiac sensor 120 is used to monitor and acquire cardiac electrical signals. The electrocardio detection has a plurality of lead modes, the system adopts a simulation single lead mode, takes the right leg as a driving end, adopts a right leg driving circuit, detects the potential difference of the left hand and the right hand, and amplifies and filters the potential difference to obtain the electrocardio signal of the single lead.

In one embodiment, the control circuit 200 includes a pulse signal conditioning circuit 210, a cardiac signal conditioning circuit 220, and a signal processor 230.

The pulse signal conditioning circuit 210 is connected with the pulse sensor 110 and the signal processor 230 respectively, the pulse signal conditioning circuit 210 comprises a primary amplifying circuit, a band-pass filter, a power frequency wave limiter, a secondary amplifying circuit and a voltage adding circuit, the input end of the primary amplifying circuit is connected with the pulse sensor 110, the input end of the band-pass filter is connected with the output end of the primary amplifying circuit, the input end of the power frequency wave limiter is connected with the output end of the band-pass filter, the input end of the secondary amplifying circuit is connected with the output end of the power frequency wave limiter, the input end of the voltage adding circuit is connected with the output end of the secondary amplifying circuit, and the output end of the voltage adding circuit is connected with the signal processor 230.

The electrocardiosignal conditioning circuit 220 is respectively connected with the electrocardio sensor 120 and the signal processor 230, the electrocardiosignal conditioning circuit 220 comprises a differential amplifying circuit, a band-pass filter, a power frequency wave limiter, a secondary amplifying circuit and a voltage adding circuit, the input end of the differential amplifying circuit 220 is connected with the electrocardio sensor 120, the input end of the band-pass filter is connected with the output end of the differential amplifying circuit, the input end of the power frequency wave limiter is connected with the output end of the band-pass filter, the input end of the secondary amplifying circuit is connected with the output end of the power frequency wave limiter, the input end of the voltage adding circuit is connected with the output end of the secondary amplifying circuit, and the output end of the voltage adding circuit is connected with the.

The signal processor 230 is connected to the ion-phoresis drug delivery device 300, and is configured to receive the physiological electrical signal processed by the signal conditioning circuit, perform signal modulation and digital-to-analog conversion, obtain a blood pressure value corresponding to the physiological electrical signal, determine a blood pressure range to which the blood pressure value belongs, generate a control instruction including a start of release of the drug or a stop of release of the drug, and send the control instruction to the ion-phoresis drug delivery device 300.

In one embodiment, the control circuit 200 further includes a data transmission module and a power module 260.

The data transmission module includes a serial port module 240 and a bluetooth module 250, which are respectively connected to the signal processor 230, and is configured to transmit the acquired physiological electrical signal and the obtained blood pressure value to the PC terminal 400 or the mobile phone terminal 500, receive a control instruction generated by the PC terminal 400 or the mobile phone terminal 500 according to the physiological electrical signal and the blood pressure value, and send the control instruction to the ion-phoresis drug administration device 300. It is understood that the PC end 400 or the mobile phone end 500 may be replaced by a server, a personal digital assistant, a tablet computer, etc. The server, the PC terminal 400, the mobile phone terminal 500, the personal digital assistant, and the tablet computer may be collectively referred to as a control device.

And the power supply module 260 is used for supplying power to the electrocardiosignal conditioning circuit 220, the pulse signal conditioning circuit 210 and the signal processor 230.

In one embodiment, the iontophoretic drug delivery device 300 includes an iontophoretic drug delivery circuit and an iontophoretic drug delivery device.

The ion-electrophoresis administration circuit is connected with the signal processor 230 of the control circuit 200 and used for receiving an administration starting instruction or an administration stopping instruction and controlling the ion-electrophoresis administration device to carry out drug start release or drug stop release.

The ion electrophoresis administration device is connected with the ion electrophoresis administration circuit, and the ion electrophoresis administration device can contain the medicine inside.

In one embodiment, as shown in fig. 2, the signal processor 230 selects an STM32 main control chip circuit, and is composed of an STM32F103RET6, an inductor L1, a capacitor C23, a capacitor C24, a light emitting diode D4, a resistor R35, a capacitor C14, a capacitor C15, a capacitor C16, a resistor R21, a crystal oscillator X2, a capacitor C25, a capacitor C29, a resistor R24, a capacitor C36, and a key S1. The inductor L1, the capacitors C23 and C24 are connected to realize conversion from digital power supply, digital ground to analog power supply and analog ground, and the three capacitors C14, C15 and C16 form a filter circuit of the power supply of the main control chip. The resistor R21 is connected IN parallel with the crystal oscillator, two sides of the resistor R21 are respectively connected with a capacitor C25 and a capacitor C29, the other side of the capacitor is grounded to form a crystal oscillator circuit, and two ends of the crystal oscillator circuit are respectively connected with the PD0_ OSC _ IN of the STM32F103RET 6. The capacitor C36 is connected with the key S1 in parallel and then connected with R24 in series to form a reset circuit, and the reset circuit is connected with the NRST pin of the STM32F103RET 6. The light emitting diode D4 is connected in series with the resistor R35, and the other end of R35 is connected with the PA3 pin of STM32F103RET 6. Pins VBAT, VDD _1, VDD _2, VDD _3, and VDD _4 of STM32F103 are connected to VCC _3V3, and pins VSS _1, VSS _2, VSS _3, and VSS _4 are connected to GND.

The pulse sensor 110 is connected with the pulse signal conditioning circuit 210 through a lead, and the electrocardio sensor 120 is connected with the electrocardio signal conditioning circuit 220 through a lead. The electrocardiosignal conditioning circuit 220 and the pulse signal conditioning circuit 210 are respectively connected with a pin PA0 and a pin PA1 of an STM32 main control chip circuit through PCB copper wires, and the STM32 main control chip circuit adopts STM32F103RET 6. And a TXD pin and an RXD pin of the serial port module are respectively connected with a PA10 pin and a PA9 pin of the STM32 main control chip circuit through PCB copper wires. The P16 pin and the P17 of the Bluetooth module are connected with the PB11 pin and the PB10 pin of the STM32 main control chip circuit through PCB copper wire pins respectively. All power supplies of the control circuit are provided by the power supply module 260, the power supply mode can select wired power supply of a USB wire and power supply of a self-contained battery, and four different power supplies of 3V, 3.3V, -5V and 5V can be provided. The PC terminal 400 is connected to the serial port module 240 and the power supply module 260 through USB cables, and can provide power and data transmission. The bluetooth module 250 transmits data such as electrocardio, pulse, blood pressure and the like to the PC terminal 400 or the mobile phone terminal 500 having the bluetooth function in a wireless transmission manner. The ion electrophoresis drug delivery device 300 is connected with a PC0 pin, a PC1 pin and a PC2 pin of an STM32 main control chip circuit through leads.

In one embodiment, as shown in fig. 3, the power module 260 is composed of a micro USB1, a pin header P2, a switch SW1, a fuse F1, a capacitor C48, a capacitor C49, a transformer chip AMS1117-3.3, a capacitor C46, a capacitor C47, a resistor R46, a light emitting diode D5, a capacitor C51, a chip MAX660ESA, a capacitor C53, a capacitor C52, a button cell B1, a button cell B2, and a button cell B3. Pin 1 of the microUSB USB1 is connected with pin 1 of a pin header P2, pin header 2 is connected with

pins

4 and 5 of a switch SW1, and pin header 3 is connected with a series circuit of two button electromagnetics B1 and B2. The pin 6 of the key SW1 is connected with a fuse, and the other end of the fuse is connected with a filter circuit formed by a capacitor C48 and a capacitor C49 and a pin 3 of a transformation chip AMS 1117-3.3. The transformer chip pins 2 and 4 are connected with a parallel circuit of a capacitor C46 and a capacitor C47, a series circuit of a resistor R46 and a light-emitting diode D5. A capacitor C51 is connected in series between

pins

2 and 4 of the voltage transformation chip MAX660ESA, a pin 8 is connected with VCC _5V, and a pin 5 is connected with a parallel circuit of a capacitor C53 and a capacitor C52.

In one embodiment, as shown in fig. 4, the serial port module 240 is composed of a CH340 chip U2, a crystal oscillator X1, a capacitor C4, a capacitor C5, a capacitor C1, a capacitor C2, a diode D1, a resistor R1, a resistor R2, a transistor Q1, a resistor R3, a transistor Q2, and a resistor R5. Pin 2 and pin 3 of the CH340 chip are connected to pins PA9 and PA10 of STM32F103RET6, respectively, and pin 5 and pin 6 are connected to pins D + and D-of microUSB 1. The crystal oscillator X1, the capacitor C4 and the capacitor C5 form a crystal oscillator circuit, and two ends of the crystal oscillator circuit are connected with the pin 7 and the pin 8 of the CH340 chip U2. Pin 13 of a chip U2 of CH340 is connected with one end of a resistor R2, the other end of the resistor R2 is connected with the base electrode of a triode Q1, the pole electrode of the Q1 is connected with a resistor R1 and one end of a diode, the other end of the resistor R1 is connected with VCC _3V3, and the other end of the diode D1 is connected with the NRST pin of STM32F103RET 6. An emitter of the triode Q1 is connected with a pin 14 of a CH340 chip U2 and one end of a resistor R3, the other end of the resistor R3 is connected with a base of the triode Q2, a collector of the triode Q2 is connected with VCC _3V3, one end of an emitter region resistor R5 is connected, and the other end of the resistor R5 is connected with a BOOT0 pin of an STM32F103RET 6.

In one embodiment, as shown in fig. 5, the bluetooth module 250 is composed of CC2641 bluetooth, a resistor R4, a light emitting diode D2, a resistor R6, a light emitting diode D3, and a key S2. Pin 7, pin 14 and pin 15 of the CC2641 bluetooth are respectively connected to pins NRST, PB11 and PB10 of STM32F103RET6, pin 9 is connected to one end of a light emitting diode D2, the other end of the light emitting diode D2 is connected to one end of a resistor R4, the other end of the resistor R4 is connected to GFD, pin 10 is connected to light emitting diode D3, the other end of the light emitting diode is connected to one end of a resistor R6, the other end of the resistor R6 is connected to GND, pin 11 is connected to one end of a key S2, the other end of the key is connected to GND, pin 1 is connected to VCC _3V3, and pin 2 is connected to GND.

In one embodiment, as shown in fig. 6, the ion-phoresis drug delivery circuit is composed of a TLC5615 chip U7, a capacitor C55, a capacitor C56, a resistor R56, a resistor R58, a programmable single-node transistor Q3, an INA122 chip U6, a capacitor C54, a capacitor C58, an OP07 chip IC9, a capacitor C57, a capacitor C59, a resistor R57, and a resistor R59. Pin 1, pin 2 and pin 3 of the TLC5615 chip U7 are respectively connected with PC0, PC1 and PC2 of STM32F103RET6, pin 5 is connected with GND, and pin 8 is connected with VCC _5V and is filtered by a parallel circuit of a capacitor C55 and a capacitor C56. Pin 6 is connected with resistor R58 and one end of programmable single-node transistor Q3, and the other end of resistor R58 is connected with VCC _5V, and the other end of programmable single-node transistor Q3 is connected with GND, and pin 3 of programmable single-node transistor Q3 is connected with pin 1. Pin 7 of TLC5615 chip U7 is connected to one end of resistor R56 and the other end of resistor R56 is connected to pin 3 of INA122 chip U6. Pin 2 of the INA122 chip is connected with GND, pin 7 is connected with VCC _5V and is filtered through a capacitor C54, pin 4 is connected with VEE _5V and is filtered through a capacitor C58, and pin 6 is connected with a resistor R57. The other end of the resistor R57 is connected with the pin 3 of the resistor R59 and the OP07 operational amplifier IC9, and the other end of the resistor R59 is connected with GND. Pin 4 of OP07 opamp IC9 is connected to VEE _5V and filtered by capacitor C57, pin 7 is connected to VCC _5V and filtered by capacitor C59, and pin 2 is connected to pin 5 of INA122 chip U6.

In one embodiment, as shown in fig. 7, the ecg signal conditioning circuit 220 comprises a right leg driving circuit, a differential amplifier circuit, a band-pass filter, a power frequency limiter, a secondary amplifier circuit, and a voltage adder circuit. The right leg driving circuit is composed of an operational amplifier IC1A, a capacitor C10, a capacitor C20, a resistor R19, a capacitor C28 and a resistor R22. Pin 4 of the operational amplifier IC1A is connected with VEE _5V and filtered through a capacitor C10, pin 8 is connected with VCC _5V and filtered through C20, a capacitor C28 is connected with a resistor R22 in series and connected with R19 in parallel, pin 2 of IC1A is connected with pin 1 through a parallel circuit, and pin 1 is connected with a right leg lead wire. The differential amplification circuit is composed of a resistor R7, a resistor R11, a resistor R12, a capacitor C18, a capacitor C26 and an AD620 differential operational amplifier IC 2. The resistor R7 is connected with the resistor R12 in series, the series end is connected with the pin 2 of the operational amplifier IC1A, the resistor R11 is connected in parallel after the series connection, and the two ends of the parallel circuit are respectively connected with the pin 1 and the pin 8 of the operational amplifier IC 2. The operational amplifier pin 7 is connected with VCC _5V and filtered by C18, the operational amplifier pin 4 is connected with VEE _5V and filtered by a capacitor C26, and the pin 6 is connected with the band-pass filter. The band-pass filter is composed of a capacitor C8, a capacitor C9, a resistor R13, a resistor R8, a capacitor C7, a capacitor C17, a capacitor C21, a resistor R17, a resistor R18, a capacitor C27, an operational amplifier IC3A and an operational amplifier IC3B, wherein the IC3A and the IC3B are disassembled by double operational amplifiers. One end of the capacitor C8 is connected with the pin 6 of the operational amplifier IC2, and the other end is connected with one end of the capacitor C9 and the resistor R13. The other end of the capacitor C9 is connected to the resistor R8 and the pin 3 of the operational amplifier IC3A, and the other end of the resistor R13 is connected to one end of the resistor R17, and the pin 1 and the pin 2 of the operational amplifier IC 3A. The other end of the resistor R8 is connected with GND, and the other end of the resistor R17 is connected with one end of the resistor R18 and one end of the capacitor C27. The other end of the resistor R18 is connected with a capacitor C21, the other end of the capacitor C27 is connected with a pin 6 and a pin 7 of the operational amplifier IC3B, and the other end of the capacitor C21 is connected with GND. Pin 8 of IC3A is connected with VCC _5V and filtered by capacitor C7, pin 4 is connected with VEE _5V and filtered by capacitor C17, and pin 7 of operational amplifier IC3B is connected with power frequency limiter. The power frequency wave limiter is composed of a resistor R9, a resistor R10, a capacitor C11, a capacitor C12, a capacitor C19, a capacitor C22, a resistor R14, a resistor R16, an operational amplifier IC4A, an operational amplifier IC4B, a capacitor C6, a capacitor C13, a resistor R15 and a resistor R20. The resistor R9 is connected with the resistor R10 in series, the capacitor C11 is connected with the capacitor C12 in series, the series circuit is connected in parallel, one end of the parallel connection is connected with the pin 7 of the IC3B, and the other end of the parallel connection is connected with the pin 3 of the IC 4A. The capacitor C19 is connected in parallel with the capacitor C22, the connection end of the resistor R9 and the resistor R10 at one end of the parallel circuit is connected, and the other end of the parallel circuit is connected with the pin 7 of the operational amplifier IC 4B. The resistor R14 is connected with the resistor R16 in parallel, one end of the parallel circuit is connected with the connection end of the capacitor C11 and the capacitor C12, and the other end of the parallel circuit is connected with the pin 7 of the operational amplifier IC 4B. Pin 7 of IC4B is connected to pin 6, and pin 5 is connected in series with one end of resistors R15 and R20. The other end of the resistor R20 is connected to GND, and the other end of the resistor R15 is connected to pin 2 and pin 1 of the operational amplifier IC 4A. Pin 8 of the operational amplifier IC4A is connected to VCC _5V and filtered through capacitor C6, pin 4 is connected to VEE _5V and filtered through capacitor C13, and pin 1 is connected to the second stage amplifier circuit. The second-stage amplifying circuit is composed of a capacitor C42, a capacitor C45, a resistor R44, a resistor R43 and an operational amplifier IC 7A. Pin 3 of the operational amplifier IC7A is connected to pin 1 of the operational amplifier IC4A, and pin 2 is connected to one end of the resistor R44 and the resistor R43. The other end of the resistor R44 is connected with pin 1 of the operational amplifier IC7A, and the other end of the resistor R43 is connected with GND. Pin 8 of the operational amplifier IC7A is connected to VCC _5V and filtered through capacitor C42, pin 4 is connected to V33_5V and filtered through capacitor C45, and pin 1 is connected to the voltage summing circuit. The voltage adding circuit comprises a resistor R53, a resistor R52, a resistor R45, a resistor R49, a resistor R50, a resistor R51 and an operational amplifier IC7B, wherein the former IC7A and the former IC7B form a double operational amplifier chip. One end of the resistor R45 is connected to pin 1 of the IC7A, and the other end is connected to one end of the resistor R49 and pin 5 of the operational amplifier IC 7B. The other end of the resistor R49 is connected with one ends of the resistor R53 and the resistor R54. The other end of the resistor R53 is connected to GND, and the other end of the resistor R52 is connected to VCC _ 5V. The operational amplifier IC7B is connected with one end of the resistor R50 and the resistor R51, and the other end is connected with the PA1 of the STM32F103RET 6. The other end of the resistor R50 is connected with GND, and the other end of the resistor R51 is connected with a pin 7 of the operational amplifier IC 7B.

In one embodiment, as shown in fig. 8, the pulse signal conditioning circuit 210 is composed of a primary amplifying circuit, a band-pass filter, a power frequency limiter, a secondary amplifying circuit, and a voltage adding circuit. The primary amplification circuit is connected with a resistor R28, a resistor R30, a resistor R31 and an operational amplifier IC1B, wherein the former operational amplifier IC1A and the operational amplifier IC1B form a double operational amplifier chip IC 1. Pin 1 of the operational amplifier IC1B is connected to R28, pin 6 is connected to one end of a resistor R30 and a resistor R31, and pin 7 is connected to the band pass filter. The other end of the resistor R28 is connected with the signal input end, the other end of the resistor R20 is connected with GND, and the resistor R31 is connected with a pin 7 of the operational amplifier IC 1B. The band-pass filter is composed of a capacitor C32, a capacitor C33, a resistor R25, a resistor R29, a capacitor C31, a capacitor C38, a resistor R36, a resistor R37, a capacitor C40, a capacitor C43, an operational amplifier IC5A and an operational amplifier IC5B, wherein the operational amplifier IC5A and the IC5B form a double operational amplifier chip IC 5. One end of the capacitor C32 is connected to the pin 7 of the operational amplifier IC1B, and the other end is connected to one end of the resistor R29 and the capacitor C33. The other end of the resistor R29 is connected with one end of a pin 2 and a pin 6 of the operational amplifier IC5A and one end of a resistor R36, and the other end of the capacitor R33 is connected with one end of a pin 3 of the operational amplifier IC5A and one end of a resistor R25. The other end of the resistor R25 is connected with GND, and the other end of the capacitor R36 is connected with one end of the resistor R37 and one end of the capacitor C43. The other end of the resistor R37 is connected with a pin 5 of the capacitor C40 and the operational amplifier IC5B, the other end of the capacitor C43 is connected with a pin 6 and a pin 7 of the operational amplifier IC5B, and the other end of the capacitor C0 is connected with GND. Pin 8 of the operational amplifier IC5A is connected with VCC _5V and filters through a capacitor C31, pin 4 is connected with VEE _5V and filters through a capacitor C38, and pin 1 is connected with a power frequency limiter. The power frequency wave limiter is composed of a resistor R26, a resistor R27, a capacitor C34, a capacitor C35, a capacitor C39, a capacitor C41, a resistor R32, a resistor R34, a capacitor C30, a capacitor C37, a resistor R33, a resistor R38, an operational amplifier IC6A and an operational amplifier IC6B, wherein the operational amplifier IC6A and the IC6B form a double operational amplifier chip. The resistor R26 is connected with the resistor R27 in series, the capacitor C34 is connected with the capacitor C35 in series, the two series circuits are connected in parallel, one end of the parallel circuit is connected with a pin 1 of the operational amplifier IC5A, and the other end of the parallel circuit is connected with a pin 3 of the operational amplifier IC 6A. The capacitor C39 is connected with the capacitor C41 in parallel, one end of the parallel circuit is connected with the connection end of the resistor R26 and the resistor R27, and the other end of the parallel circuit is connected with the pin 7 of the operational amplifier IC 6B. The resistor R32 is connected in parallel with the resistor R34, one end of the parallel circuit is connected with the connection end of the capacitor C34 and the capacitor C35, and the other end of the parallel circuit is connected with the pin 7 of the operational amplifier IC 6B. Pin 6 of the operational amplifier IC6B is connected to pin 7, and pin 5 is connected to one end of the resistor R38 and resistor R33. The other end of the resistor R38 is connected to GND, and the other end of the resistor R33 is connected to pin 2 and pin 1 of the operational amplifier IC 6A. Pin 8 of the operational amplifier IC6A is connected to VCC _5V and filtered through capacitor C30, pin 4 is connected to VEE _5V and filtered through capacitor C37, and pin 1 is connected to the second stage amplifier circuit. The second-stage amplifying circuit is composed of a resistor R54, a resistor R55, a capacitor C44, a capacitor C50 and an operational amplifier IC 8A. Pin 3 of IC8A is connected to pin 1 of IC6A, and pin 2 is connected to one end of resistor R54 and resistor R55. The other end of the resistor R54 is connected to GND, and the other end of the resistor R55 is connected to pin 1 of IC 8A. Pin 8 of IC8A is connected to VCC _5V and filtered through capacitor C44, pin 4 is connected to VEE _5V and filtered through capacitor C50, and pin 1 is connected to the voltage summing circuit. The voltage adding circuit is composed of a resistor R39, a resistor R40, a resistor R41, a resistor R42, a resistor R47, a resistor R48 and an operational amplifier IC8B, wherein the previous operational amplifier IC8A and IC8B form a double operational amplifier chip. One end of the resistor R42 is connected with the pin 1 of the operational amplifier IC8A, and the other end is connected with one end of the resistor R41 and the pin 5 of the operational amplifier IC 8B. The other end of the resistor R41 is connected with one end of the resistor R39 and one end of the resistor R40. The other end of the resistor R39 is connected to VCC _5V, and the other end of the resistor R40 is connected to GND. Pin 6 of the operational amplifier IC8B is connected to one end of a resistor R47 and a resistor R48, and pin 7 is connected to pin PA2 of STM32F103RET 6. The other end of the resistor R47 is connected with GND, and the other end of the resistor R48 is connected with a pin 7 of the operational amplifier IC 8B.

In one embodiment, as shown in fig. 9, the signal processor 230 is configured to perform digital filtering on the acquired pulse electrical signal and the acquired electrocardiographic signal, extract peaks from the pulse electrical signal and the electrocardiographic signal, respectively, subtract the time coordinate of the peak of the electrocardiographic signal from the time coordinate of the peak of the pulse electrical signal to obtain the pulse transmission time PTT, set a threshold according to the heart rate of the tester, and reject singular values of the PTT. The method comprises the following steps: the peak value extraction comprises pulse peak value extraction and electrocardio peak value extraction, and due to the movement of a human body, baselines of pulse signals and electrocardio signals have larger fluctuation. If the threshold method is directly adopted, a plurality of wrong points can be extracted, so that the first derivative of the electrocardiosignal and the pulse electric signal is firstly obtained, and the time coordinate of the maximum value of the first derivative is obtained. The peak values of the electrocardiosignal and the pulse signal are both after the first derivative and are close in time, so that the maximum value of 100 points of the original signal after the time is obtained by taking the maximum value of the first derivative as a starting point, namely the peak values of the electrocardiosignal and the pulse signal. After the peak value of the electrocardio pulse is obtained, the pulse transmission time PTT can be solved by subtracting the electrocardio peak value time coordinate from the corresponding pulse peak value time coordinate. In order to further improve the accuracy of the pulse transmission time PTT, singular points in the pulse transmission time PTT need to be removed, and since the range of the pulse transmission time PTT varies from person to person, different thresholds need to be set for different persons to remove singular values. Acquiring a heart rate, and calculating the time period of the electrocardio-pulse according to the heart rate, wherein the time period of the electrocardio-pulse is the time period of a heart beat, and 2/5 of the time period can be set as an upper threshold value and 1/5 of the time period can be set as a lower threshold value according to test experience. If the calculated pulse transmission time PTT is within the threshold value range, the pulse transmission time PTT is reserved, otherwise, the pulse transmission time PTT is taken as a singular value to be removed. Calculating a blood pressure value:

DBP＝(SBP_0)/3+(2DBP_0)/3+Aln((PTT_0)/PTT)-((SBP_0-DBP_0))/3(PTT_0^2)/(PTT^2)

SBP＝DBP+(SBP_0-DBP_0)(PTT_0^2)/(PTT^2)

the blood pressure value comprises a diastolic pressure DBP and a systolic pressure SBP, PTT is pulse transmission time, DBP _0 is a preset calibration value of the diastolic pressure, SBP _0 is a preset calibration value of the systolic pressure, and PTT _0 is a preset calibration value of the pulse transmission time. The specific relationship between the blood pressure of each person and the pulse transmission time is different, and the same person can change with time, so that the blood pressure needs to be calculated by a group of calibration values at intervals. And acquiring a group of blood pressure values by using a sphygmomanometer with high accuracy, acquiring a group of electrocardio-pulse data, calculating pulse transmission time and averaging the pulse transmission time to obtain DBP _0, SBP _0 and PTT _ 0.

The signal processor 230 is further configured to determine a blood pressure value corresponding to the acquired physiological electrical signal, determine that the blood pressure value is within a high blood pressure range if the blood pressure value is higher than a blood pressure threshold, and determine that the blood pressure value is within a normal blood pressure range if the blood pressure value is not greater than the blood pressure threshold;

if the blood pressure value is in the high blood pressure range, the signal processor generates a medicine administration starting instruction;

if the blood pressure value is in the normal blood pressure range, the signal processor generates a medicine administration stopping instruction.

In the embodiment, the peak values of the pulse electric signals and the electrocardiosignals are obtained by processing the pulse electric signals and the electrocardiosignals, the pulse transmission time PTT of the peak values of the pulse electric signals and the electrocardiosignals is set according to the heart rate, the singular values of the PTT are removed to obtain the accurate blood pressure value, whether the drug is administered or not is judged according to the blood pressure value, and the purposes of automatically administering the drug in real time and accurately regulating and controlling the blood pressure can be achieved.

In one embodiment, as shown in fig. 10, there is provided a drug release control method comprising:

acquiring a physiological electrical signal;

In one embodiment, the acquired pulse electrical signals and the acquired electrocardiosignals are subjected to digital filtering, peak values of the pulse electrical signals and the electrocardiosignals are respectively extracted, pulse transmission time PTT is obtained by subtracting the time coordinate of the electrocardiosignal peak value from the time coordinate of the pulse electrical signal peak value, a threshold value is set according to the heart rate of a tester, and singular values of the PTT are removed. The method comprises the following steps: the peak value extraction comprises pulse peak value extraction and electrocardio peak value extraction, and due to the movement of a human body, baselines of pulse signals and electrocardio signals have larger fluctuation. If the threshold method is directly adopted, a plurality of wrong points can be extracted, so that the first derivative of the electrocardiosignal and the pulse electric signal is firstly obtained, and the time coordinate of the maximum value of the first derivative is obtained. The peak values of the electrocardiosignal and the pulse signal are both after the first derivative and are close in time, so that the maximum value of 100 points of the original signal after the time is obtained by taking the maximum value of the first derivative as a starting point, namely the peak values of the electrocardiosignal and the pulse signal. After the peak value of the electrocardio pulse is obtained, the pulse transmission time PTT can be solved by subtracting the electrocardio peak value time coordinate from the corresponding pulse peak value time coordinate. In order to further improve the accuracy of the pulse transmission time PTT, singular points in the pulse transmission time PTT need to be removed, and since the range of the pulse transmission time PTT varies from person to person, different thresholds need to be set for different persons to remove singular values. Acquiring a heart rate, and calculating the time period of the electrocardio-pulse according to the heart rate, wherein the time period of the electrocardio-pulse is the time period of a heart beat, and 2/5 of the time period can be set as an upper threshold value and 1/5 of the time period can be set as a lower threshold value according to test experience. If the calculated pulse transmission time PTT is within the threshold value range, the pulse transmission time PTT is reserved, otherwise, the pulse transmission time PTT is taken as a singular value to be removed. Calculating a blood pressure value:

DBP＝(SBP_0)/3+(2DBP_0)/3+Aln((PTT_0)/PTT)-((SBP_0-DBP_0))/3(PTT_0^2)/(PTT^2)

SBP＝DBP+(SBP_0-DBP_0)(PTT_0^2)/(PTT^2)

Judging a blood pressure value corresponding to the acquired physiological electric signal, if the blood pressure value is higher than a blood pressure threshold value, determining that the blood pressure value is in a high blood pressure range, and if the blood pressure value is not greater than the blood pressure threshold value, determining that the blood pressure value is in a normal blood pressure range;

It should be understood that, although the various steps in the flowcharts of fig. 9-10 are shown in order as indicated by the arrows, the steps are not necessarily performed in order as indicated by the arrows. The steps are not performed in the exact order shown and described, and may be performed in other orders, unless explicitly stated otherwise. Moreover, at least some of the steps in fig. 9-10 may include multiple steps or multiple stages, which are not necessarily performed at the same time, but may be performed at different times, which are not necessarily performed in sequence, but may be performed in turn or alternately with other steps or at least some of the other steps or stages.

In one embodiment, a computer-readable storage medium is provided, having a computer program stored thereon, which when executed by a processor, performs the steps of:

acquiring a physiological electrical signal;

In one embodiment, the computer program when executed by the processor further performs the steps of:

the method comprises the steps of performing digital filtering on collected pulse electric signals and electrocardio signals, respectively extracting peak values of the pulse electric signals and the electrocardio signals, subtracting the time coordinate of the peak value of the electrocardio signals from the time coordinate of the peak value of the pulse electric signals to obtain pulse transmission time PTT, setting a threshold value according to the heart rate of a tester, and removing singular values of the PTT. The method comprises the following steps: the peak value extraction comprises pulse peak value extraction and electrocardio peak value extraction, and due to the movement of a human body, baselines of pulse signals and electrocardio signals have larger fluctuation. If the threshold method is directly adopted, a plurality of wrong points can be extracted, so that the first derivative of the electrocardiosignal and the pulse electric signal is firstly obtained, and the time coordinate of the maximum value of the first derivative is obtained. The peak values of the electrocardiosignal and the pulse signal are both after the first derivative and are close in time, so that the maximum value of 100 points of the original signal after the time is obtained by taking the maximum value of the first derivative as a starting point, namely the peak values of the electrocardiosignal and the pulse signal. After the peak value of the electrocardio pulse is obtained, the pulse transmission time PTT can be solved by subtracting the electrocardio peak value time coordinate from the corresponding pulse peak value time coordinate. In order to further improve the accuracy of the pulse transmission time PTT, singular points in the pulse transmission time PTT need to be removed, and since the range of the pulse transmission time PTT varies from person to person, different thresholds need to be set for different persons to remove singular values. Acquiring a heart rate, and calculating the time period of the electrocardio-pulse according to the heart rate, wherein the time period of the electrocardio-pulse is the time period of a heart beat, and 2/5 of the time period can be set as an upper threshold value and 1/5 of the time period can be set as a lower threshold value according to test experience. If the calculated pulse transmission time PTT is within the threshold value range, the pulse transmission time PTT is reserved, otherwise, the pulse transmission time PTT is taken as a singular value to be removed. Calculating a blood pressure value:

DBP＝(SBP_0)/3+(2DBP_0)/3+Aln((PTT_0)/PTT)-((SBP_0-DBP_0))/3(PTT_0^2)/(PTT^2)

SBP＝DBP+(SBP_0-DBP_0)(PTT_0^2)/(PTT^2)

It will be understood by those skilled in the art that all or part of the processes of the methods of the embodiments described above can be implemented by hardware instructions of a computer program, which can be stored in a non-volatile computer-readable storage medium, and when executed, can include the processes of the embodiments of the methods described above. Any reference to memory, storage, database or other medium used in the embodiments provided herein can include at least one of non-volatile and volatile memory. Non-volatile Memory may include Read-Only Memory (ROM), magnetic tape, floppy disk, flash Memory, optical storage, or the like. Volatile Memory can include Random Access Memory (RAM) or external cache Memory. By way of illustration and not limitation, RAM can take many forms, such as Static Random Access Memory (SRAM) or Dynamic Random Access Memory (DRAM), among others.

In the description herein, references to the description of "some embodiments," "other embodiments," "desired embodiments," etc., mean that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the invention. In this specification, a schematic description of the above terminology may not necessarily refer to the same embodiment or example.

The technical features of the above embodiments can be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the above embodiments are not described, but should be considered as the scope of the present specification as long as there is no contradiction between the combinations of the technical features.

The above-mentioned embodiments only express several embodiments of the present application, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the concept of the present application, which falls within the scope of protection of the present application. Therefore, the protection scope of the present patent shall be subject to the appended claims.

Claims

1. A drug release control device is characterized by comprising a blood pressure monitoring device and an ion electrophoresis administration device;

the blood pressure monitoring device includes:

a physiological signal sensor for acquiring a physiological electrical signal;

2. The drug release control device of claim 1, wherein the control circuit comprises:

3. The drug release control device of claim 2, wherein the physiological signal sensor comprises:

the signal conditioning circuit includes:

4. The drug release control device according to claim 3, wherein the signal processor is configured to perform digital filtering on the acquired pulse electrical signal and the electrocardiographic signal, extract peaks from the pulse electrical signal and the electrocardiographic signal, obtain the pulse transmission time PTT by subtracting a time coordinate of the peak of the electrocardiographic signal from a time coordinate of the peak of the pulse electrical signal, obtain a heart rate from the pulse transmission time PTT, obtain a time period of the electrocardiographic pulse from the heart rate, set a threshold range according to the time period, retain the pulse transmission time PTT if the pulse transmission time PTT is within the range, otherwise remove singular values regarded as PTT, and calculate a blood pressure value:

DBP＝(SBP_0)/3+(2DBP_0)/3+Aln((PTT_0)/PTT)

-((SBP_0-DBP_0))/3(PTT_0^2)/(PTT^2)

SBP＝DBP+(SBP_0-DBP_0)(PTT_0^2)/(PTT^2)

5. The drug release control device of claim 2, wherein the blood pressure range includes a first range and a second range, and the control instructions include first instructions and second instructions to:

6. The drug release control device of claim 2, wherein the control circuit further comprises:

7. The drug release control device of claim 1, wherein the iontophoretic drug delivery device comprises:

8. A method of controlling drug release, comprising:

acquiring a physiological electrical signal;

9. The drug release control method according to claim 8, wherein the physiological electrical signals include a pulse electrical signal and an electrocardiographic signal, the acquired pulse electrical signal and electrocardiographic signal are digitally filtered, peaks are respectively extracted from the pulse electrical signal and the electrocardiographic signal, a pulse transmission time PTT is obtained by subtracting a time coordinate of the peak of the electrocardiographic signal from a time coordinate of the peak of the pulse electrical signal, a heart rate is obtained from the pulse transmission time PTT, a time period of the electrocardiographic pulse is obtained from the heart rate, a threshold range is set according to the time period, if the pulse transmission time PTT is within the range, the pulse transmission time PTT is retained, otherwise, a singular value of the PTT is removed, and a blood pressure value is calculated:

DBP＝(SBP_0)/3+(2DBP_0)/3+Aln((PTT_0)/PTT)

-((SBP_0-DBP_0))/3(PTT_0^2)/(PTT^2)

SBP＝DBP+(SBP_0-DBP_0)(PTT_0^2)/(PTT^2)

10. A computer-readable storage medium, having a computer program stored thereon, wherein the computer program, when being executed by a processor, is adapted to carry out the steps of the method for drug release control according to any of the claims 8 to 9.