A low-power automatic monitoring device for patient urine volume

Abstract

The present invention provides a low-power consumption patient urine volume automatic monitoring device, which belongs to the field of patient urine volume automatic monitoring, and includes a liquid inlet solenoid valve, a liquid inlet solenoid valve driving circuit, a liquid outlet solenoid valve, a liquid outlet solenoid valve driving circuit, a filling detection electrode, a filling detection circuit, an emptying detection electrode, an emptying detection circuit, a urine collecting tube, a single-chip microcomputer control circuit, a power management module, a data storage module, a wireless transmission module, a display module, a button control module, and a clock module. The present invention adopts a divide-and-conquer approach, divides the patient's urine into unit volumes and then counts them, and the product of the count value and the unit volume size is the patient's urine volume, and the hourly urine volume and urine flow rate are calculated based on this to display, store and send. The present invention adopts a low-power consumption design, monitors the patient's urine volume accurately, stably and conveniently, and overcomes the influence of urine density, urine velocity and urine bag position changes on urine volume monitoring.

Description

Technical Field

[0001] The present application belongs to the field of design of automatic patient urine volume monitoring devices, and in particular to a low-power automatic patient urine volume monitoring device. Background Art

[0002] Urine flow can not only directly reflect renal perfusion and renal function, but also indirectly reflect the body's hemodynamic state. It is one of the effective indicators for evaluating circulating blood volume, cardiac function and microcirculatory perfusion, and is also an important physiological indicator for fluid resuscitation and early identification of acute kidney injury. Commonly used urine flow indicators in clinical practice include urine flow per minute, urine flow per hour, 24-hour urine flow, and 48-hour urine flow. Accurate measurement of urine flow is of great significance for understanding the patient's condition, adjusting the treatment plan in a timely manner, and judging the disease progression and prognosis. It can also greatly reduce the workload of clinical nursing staff. In recent years, there have been more and more studies on automatic urine flow monitoring, and several automatic urine flow monitoring devices have appeared on the market. However, automatic urine flow monitoring devices are not widely used in clinical practice, and manual methods such as measuring cylinders and mother-and-child urine bags are still used for measurement. The main methods and shortcomings of automatic urine flow monitoring devices are currently as follows.

[0003] 1. Drop count method: By calibrating the volume of urine drops, the urine flow is converted into urine drops for counting to obtain the urine volume. After the urine flow is converted into urine drops, the amount of urine that can pass through the device per unit time is not large. When the patient's urine volume is large, it will cause a certain degree of urine accumulation and fail to achieve real-time effect, and may even affect the patient's normal urination. In addition, the composition of urine will change with the treatment plan and the patient's renal function status, and its viscosity will change, so the shape and size of the urine drop will also change, that is, the volume corresponding to the urine drop will change. The error caused by this reason will accumulate over the monitoring time.

[0004] 2. Gravimetric measurement: The weight of urine discharged by the patient is monitored in real time, and then converted into volume based on the urine density. In a ward where the monitoring environment is unstable and uncontrollable, it is difficult to ensure that the urine bag weighing state remains unchanged. The change of urine density with the treatment plan and renal function status will cause errors in the conversion of weight to volume, and the emptying process of the urine bag after it is full cannot be monitored.

[0005] 3. Volumetric measurement method: The liquid level of a fixed-volume container is monitored by a liquid level sensor, and the urine volume is directly obtained. Fluctuations and changes in the liquid level caused by the shaking of the urine bag or changes in body position will affect the measurement results of the volumetric measurement method. Similarly, it is impossible to monitor the emptying process of the urine bag.

[0006] 4. Flow rate measurement method: Use a flow rate sensor to directly measure urine flow. Due to the changes in urine composition, it is difficult to establish an accurate flow rate mathematical model, and calibration is required before use. In addition, the flow rate sensor is difficult to accurately monitor low flow rates. Summary of the invention

[0007] The present invention aims to provide a stable, accurate, convenient and low-power consumption automatic monitoring device for patient urine volume.

[0008] The solution adopted by the present invention to solve its technical problems is: a low-power consumption patient urine volume automatic monitoring device, characterized in that it includes a liquid inlet solenoid valve, a liquid inlet solenoid valve driving circuit, a liquid outlet solenoid valve, a liquid outlet solenoid valve driving circuit, a filling detection electrode, a filling detection circuit, an emptying detection electrode, an emptying detection circuit, a urine collecting tube, a single-chip control circuit, a power management module, a data storage module, a wireless transmission module, a display module, a key control module, and a clock module; the urine collecting tube is connected between the liquid inlet solenoid valve and the liquid outlet solenoid valve; the filling detection electrode is located at the connection between the urine collecting tube and the liquid inlet solenoid valve and the distance between the two pole pieces is the maximum value, and is connected to the filling detection circuit; the filling detection circuit is connected to the analog-to-digital conversion AD port of the single-chip control circuit; the emptying detection electrode is located at the connection between the urine collecting tube and the liquid outlet solenoid valve and the distance between the two pole pieces is the maximum value, and is connected to the emptying detection circuit; the The emptying detection circuit is connected to the analog-to-digital conversion AD port of the single-chip control circuit; the liquid inlet solenoid valve drive circuit is connected between the liquid inlet solenoid valve and the IO port of the single-chip control circuit; the liquid outlet solenoid valve drive circuit is connected between the liquid outlet solenoid valve and the IO port of the single-chip control circuit; the power management module, the data storage module, the wireless transmission module, the display module, the button control module, and the clock module are all connected to the single-chip control circuit; the single-chip control circuit controls the opening and closing of the liquid inlet solenoid valve and the liquid outlet solenoid valve according to the conduction state of the filling detection electrode and the emptying detection electrode, so that the urinary collecting tube is filled and emptied, thereby realizing the discharge of the patient's urine in unit volume, counting the number of times the urinary collecting tube is filled, and the product of the count value and the volume of the urinary collecting tube is the patient's urine volume, and the hourly urine volume and urine flow rate are calculated based on this for display, storage and transmission.

[0009] Optionally, the liquid inlet solenoid valve and the liquid outlet solenoid valve both adopt two-way bistable pulse solenoid water valves; the liquid inlet solenoid valve drive circuit and the liquid outlet solenoid valve drive circuit both adopt field effect transistor H-bridge drive circuit; the volume of the urine collecting tube is a constant, and its volume determines the accuracy of urine volume monitoring.

[0010] The beneficial effects of the present invention are: the monitoring device is simple, the measurement is accurate, stable and reliable, and it is easy to use. It avoids errors caused by changes in urine density and urine bag position, and can measure real-time urine volume under various flow rates. BRIEF DESCRIPTION OF THE DRAWINGS

[0011] Figure 1This is a system block diagram of the present invention.

[0012] Figure 2 It is a schematic diagram of the filling and emptying detection circuit of the present invention.

[0013] Figure 3 The figure is a program flow chart of the single chip microcomputer control circuit of the present invention. DETAILED DESCRIPTION

[0014] The implementation of the present invention is further described in detail below in conjunction with the accompanying drawings, but this embodiment is not limited to the present invention. All similar structures and similar changes of the present invention should be included in the protection scope of the present invention.

[0015] The system block diagram of this embodiment is as follows Figure 1As shown, a low-power automatic urine volume monitoring device for patients is characterized in that it includes a liquid inlet electromagnetic valve 1, a filling detection electrode 2, an emptying detection electrode 3, a liquid outlet electromagnetic valve 4, a urine collecting tube 5, a liquid inlet electromagnetic valve drive circuit 6, a filling detection circuit 7, an emptying detection circuit 8, a liquid outlet electromagnetic valve drive circuit 9, a single-chip microcomputer control circuit 10, a display module 11, a wireless transmission module 12, a button control module 13, a data storage module 14, a power management module 15, and the clock module 16; the volume of the urine collecting tube 5 is set to 1 mm Liter, that is, the urine volume monitoring accuracy is set to 1 ml; the urine collecting tube 5 is connected between the liquid inlet electromagnetic valve 1 and the liquid outlet electromagnetic valve 4; the filling detection electrode 2 is located at the connection between the urine collecting tube 5 and the liquid inlet electromagnetic valve 1 and the distance between the two poles is the maximum value, and is connected to the filling detection circuit 7; the filling detection circuit 7 is connected to the analog-to-digital conversion AD port of the single-chip control circuit 10, and the single-chip control circuit 10 adopts the ultra-low power single-chip chip STM32L151CBT6; the emptying detection electrode 3 is located at the connection between the urine collecting tube 5 and the liquid outlet solenoid valve 4 and the distance between the two pole pieces is the maximum value, and is connected to the emptying detection circuit 8; the emptying detection circuit 8 is connected to the analog-to-digital conversion AD port of the single-chip control circuit 10; the liquid inlet solenoid valve drive circuit 6 adopts an integrated MOS tube H-bridge drive circuit chip HR2125, which is connected between the liquid inlet solenoid valve 1 and the IO port of the single-chip control circuit 10; the liquid outlet solenoid valve drive circuit 4 adopts an integrated MOS tube H-bridge drive circuit chip HR2125, which is connected between the electric liquid outlet solenoid valve 9 and the IO port of the single-chip control circuit 10; the display module 11, the wireless transmission module 12, the button control module 13, the data storage module 14, the power management module 15, and the clock module 16 are all connected to the single-chip control circuit 10; the display module 11 adopts a 2.42-inch OLED screen, the wireless transmission module 12 adopts a CC2541 Bluetooth 4.0 module, and the data storage module 14 adopts a 16G SD card, the power management module 15 adopts TP4056 chip to power the entire device, and the clock module 16 adopts DS1306 clock chip.

[0016] The principle diagrams of the filling detection circuit 7 and the emptying detection circuit 8 are as follows: Figure 2 As shown, a filter capacitor C1 with a value of 0.1uF is connected between the two electrode inputs S1 and S2; the electrode input S2 is grounded, and the electrode input S1 is connected to VCC through a pull-up resistor R1 with a value of 100KΩ and is connected to the analog-to-digital conversion AD port of the microcontroller control circuit 10 through a current limiting resistor R2 with a value of 510Ω.

[0017] The program flow chart of the single chip control circuit 10 is as follows Figure 3As shown, the main program first initializes WDT, external clock, timer, ADC, UART, display module, data storage module, wireless transmission module, GUI, then turns on the interrupt and updates the GUI content in real time, and detects the input of the button control module 13. During the timer interrupt processing, the sampling rate is set to control the AD conversion. In this example, the sampling rate is set to 200Hz. In the ADC interrupt processing program, the AD conversion results of the filling detection circuit 7 and the emptying detection circuit 8 are processed. If the input of the filling detection circuit 7 is less than 3V, the liquid inlet solenoid valve 1 is closed, and the liquid outlet solenoid valve 4 is opened after a delay of 10 milliseconds; if the input of the emptying detection circuit 8 is greater than 3V, the liquid outlet solenoid valve 4 is closed, and the liquid inlet solenoid valve 1 is opened after a delay of 10 milliseconds, and the number of filling times is counted. Since the volume of the urine collecting tube 5 is a constant of 1 ml, the product of the emptying count value and the volume of the urine collecting tube is the patient's urine volume. The time is read from the clock module 16 to calculate the hourly urine volume and urine flow rate so as to be displayed on the display module 11 and saved in the data storage module 14. At the same time, the data is sent through the wireless transmission module 12.

Claims

1. A low-power patient urine volume automatic monitoring device, characterized in that: It includes a liquid inlet solenoid valve, a liquid inlet solenoid valve driving circuit, a liquid outlet solenoid valve, a liquid outlet solenoid valve driving circuit, a filling detection electrode, a filling detection circuit, an emptying detection electrode, an emptying detection circuit, a urine collecting tube, a single-chip control circuit, a power management module, a data storage module, a wireless transmission module, a display module, a key control module, and a clock module; the urine collecting tube is connected between the liquid inlet solenoid valve and the liquid outlet solenoid valve; the filling detection electrode is located at the connection between the urine collecting tube and the liquid inlet solenoid valve, and the distance between the two pole pieces is the maximum value, and is connected to the filling detection circuit; the filling detection circuit is connected to the analog-to-digital conversion AD port of the single-chip control circuit; the emptying detection electrode is located at the connection between the urine collecting tube and the liquid outlet solenoid valve, and the distance between the two pole pieces is the maximum value, and is connected to the emptying detection circuit; the emptying detection circuit is connected to the analog-to-digital conversion AD port of the single-chip control circuit Convert AD port; the liquid inlet solenoid valve drive circuit is connected between the liquid inlet solenoid valve and the IO port of the single-chip control circuit; the liquid outlet solenoid valve drive circuit is connected between the liquid outlet solenoid valve and the IO port of the single-chip control circuit; the power management module, the data storage module, the wireless transmission module, the display module, the button control module, and the clock module are all connected to the single-chip control circuit; the single-chip control circuit controls the opening and closing of the liquid inlet solenoid valve and the liquid outlet solenoid valve according to the conduction state of the filling detection electrode and the emptying detection electrode, so that the urinary collecting tube is filled and emptied, thereby realizing the discharge of the patient's urine into unit volume, counting the number of times the urinary collecting tube is filled, and the product of the count value and the volume of the urinary collecting tube is the patient's urine volume, and the urine volume and urine flow rate per hour are calculated based on this to display, store and send.

2. A low-power patient urine volume automatic monitoring device according to claim 1, characterized in that: The liquid inlet solenoid valve and the liquid outlet solenoid valve are both two-way bistable pulse solenoid valves.

3. A low-power patient urine volume automatic monitoring device according to claim 1, characterized in that: The liquid inlet electromagnetic valve driving circuit and the liquid outlet electromagnetic valve driving circuit both adopt field effect tube H-bridge driving circuit.

4. A low-power patient urine volume automatic monitoring device according to claim 1, characterized in that: The volume of the urine collecting tube is a constant, and the volume determines the accuracy of urine volume monitoring.

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