Urine drainage control and urine volume metering device and system

Abstract

The invention discloses a urine drainage control and urine volume metering device, which comprises a primary bag, a secondary bag and a urine volume metering device, the first sub-bag is provided with a urine outlet, a urine inlet and a urine inlet catheter, is arranged on the main bag and is communicated with the main bag; the first capacitive sensor is arranged on the urine inlet catheter; the controller is provided with an excitation source unit which outputs a reference alternating-current square wave signal based on a preset frequency, and the first capacitive sensor measures the urine flow in the urine inlet catheter based on the reference alternating-current square wave signal so as to generate a real-time urine flow electric signal; the signal amplification unit outputs the amplified real-time urine flow electric signal; the digitization unit is used for outputting a digitized real-time urine flow electric signal; the central processing unit is used for calculating the total urine volume based on the digitized real-time urine flow electric signal. Therefore, the measuring precision of the urine volume can be improved, the trickle of the urine can be accurately captured, and clinical treatment of a patient is effectively guaranteed.

Description

Technical Field

[0001] This invention relates to the field of medical devices, specifically to a urine drainage control and urine volume measurement device and system. Background Technology

[0002] Currently, urine drainage and urine volume measurement are key aspects of clinical diagnosis and treatment. Accurate urine volume data are important for assessing a patient's renal function, fluid balance, and disease progression.

[0003] Commonly used urine drainage and measurement devices in clinical practice mainly include graduated drainage bags and simple sensor-based measurement devices. These devices typically consist of a drainage bag body, an inlet catheter, and basic sensing components. After urine flows into the bag through the inlet catheter, the flow rate is measured manually by reading the graduations or by the sensing components, and then a simple calculation is performed to measure the urine volume. Sensor-based devices often acquire urine flow-related signals through sensors, perform simple processing, and calculate the total urine volume, meeting basic clinical measurement needs.

[0004] It is also easy to see that the existing devices lack accurate acquisition of urine flow detection signals, which easily leads to poor stability and insufficient accuracy of the flow signals, resulting in inaccurate urine volume measurement results. Summary of the Invention

[0005] The present invention aims to at least partially solve the technical problems in the above-mentioned technologies.

[0006] Therefore, the present invention discloses a urine drainage control and urine volume measurement device, comprising:

[0007] The mother bag is equipped with a urine outlet;

[0008] The first sub-bag is provided with a urination outlet, a urination inlet and a urination tube, and is located on the mother bag and communicates with the mother bag;

[0009] A first capacitive sensor is disposed on the urine inlet catheter;

[0010] The controller is configured with:

[0011] The excitation source unit outputs a reference AC square wave signal based on a preset frequency. The first capacitive sensor measures the urine flow rate in the urinary catheter based on the reference AC square wave signal to generate a real-time urine flow electrical signal.

[0012] A signal amplification unit receives the real-time urine flow electrical signal and amplifies it to output the amplified real-time urine flow electrical signal.

[0013] A digitization unit receives the amplified real-time urine flow electrical signal and digitizes it to output the digitized real-time urine flow electrical signal.

[0014] The central processing unit receives the digitized real-time urine flow electrical signal and calculates the total urine volume based on the digitized real-time urine flow electrical signal.

[0015] The urine drainage control and urine volume measurement device disclosed in this invention can improve the measurement accuracy of urine volume, accurately capture urine trickle, and effectively protect the patient's clinical treatment.

[0016] In addition, the urine drainage control and urine volume measuring device disclosed in this invention may also have the following additional technical features:

[0017] In one embodiment of the present invention, the controller is further provided with:

[0018] A reference capacitor, together with the first capacitive sensor, forms a bridge circuit and outputs a differential form of the real-time urine flow electrical signal.

[0019] In one embodiment of the present invention, the central processing unit calculates the total urine volume based on the digitized real-time urine flow electrical signal according to the following formula: ,in, The total urine volume is [the amount of urine produced]. To correct the parameters, For the first capacitive sensor in the first Real-time urine flow electrical signal generated in each sampling period The preset frequency.

[0020] In one embodiment of the present invention, it further includes:

[0021] Second sub-bag;

[0022] A second capacitive sensor is disposed on the second sub-bag;

[0023] The urinary catheter is arranged in a Z-shape on the second sub-bag, and the second capacitive sensor is arranged on the urinary catheter. The sensor measures the urine flow rate in the urinary catheter based on the reference AC square wave signal to generate a reference urine flow rate electrical signal.

[0024] In one embodiment of the present invention, the central processing unit further comprises: calculating the total urine volume based on the digitized real-time urine flow electrical signal according to the following formula: ,in, This refers to the capacitance value of the urine inlet catheter in an empty state. The reference urine flow electrical signal generated by the second capacitive sensor.

[0025] In one embodiment of the present invention, the central processing unit outputs an alarm signal according to the following steps:

[0026] S1: Generate the real-time urine flow electrical signal The time series;

[0027] S2: Based on the real-time urine flow electrical signal at the current moment Calculate the electrical signal of the real-time urine flow rate compared to the previous time step. and the real-time urine flow electrical signal at the next moment instantaneous rate of change and ;

[0028] If the instantaneous rate of change If the signs are opposite and the absolute values ​​both exceed the first preset threshold, then the alarm signal is output.

[0029] In one embodiment of the present invention, the central processing unit further outputs an alarm signal according to the following steps:

[0030] S3: If the instantaneous rate of change If the second preset threshold is exceeded and continues for a first preset time, the alarm signal is output.

[0031] Or if the instantaneous rate of change If the value is less than the third preset threshold and remains below the second preset time, then the alarm signal is output.

[0032] In one embodiment of the present invention, the controller is further provided with:

[0033] The communication unit uploads the total urine volume value to the cloud;

[0034] A clock unit that provides a clock frequency for the communication unit.

[0035] Additional features and advantages of this invention will be set forth in the description which follows, or may be learned by practicing the invention. Attached Figure Description

[0036] The technical solution and beneficial effects of the present invention will become apparent and readily understood from the following description in conjunction with the accompanying drawings, wherein:

[0037] Figure 1 This is a schematic diagram of the urine drainage control and urine volume measurement device of the present invention;

[0038] Figure 2 This is a circuit diagram of the excitation source unit, signal amplification unit, digitization unit, and central processing unit in the controller of the present invention;

[0039] Figure 3 The circuit diagram shows the bridge circuit formed by the reference capacitor and the first capacitive sensor in the controller of the present invention.

[0040] Figure 4 This is a circuit diagram of the communication unit and clock unit in the controller of the present invention.

[0041] As shown in the figure:

[0042] 101-Mother bag, 102-First daughter bag, 103-First capacitive sensor, 104-Controller, 105-Second daughter bag, 106-Second capacitive sensor. Detailed Implementation

[0043] The technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments.

[0044] The urine drainage control and urine volume measurement device disclosed in this invention will now be described with reference to the accompanying drawings.

[0045] like Figure 1 and Figure 2 As shown, a urine drainage control and urine volume measurement device includes:

[0046] Mother bag 101, which is equipped with a urine outlet;

[0047] The first sub-bag 102 is provided with a urination outlet, a urination inlet and a urination tube, and is located on the mother bag 101 and connected to the mother bag 101;

[0048] A first capacitive sensor 103 is disposed on the urinary catheter;

[0049] Controller 104 is configured with:

[0050] The excitation source unit outputs a reference AC square wave signal based on a preset frequency. The first capacitive sensor 103 measures the urine flow rate in the urinary catheter based on the reference AC square wave signal to generate a real-time urine flow electrical signal.

[0051] The signal amplification unit receives the real-time urine flow electrical signal and amplifies it to output the amplified real-time urine flow electrical signal.

[0052] The digitization unit receives the amplified real-time urine flow electrical signal and digitizes it to output the digitized real-time urine flow electrical signal.

[0053] The central processing unit receives the digitized real-time urine flow electrical signal and calculates the total urine volume based on the digitized real-time urine flow electrical signal.

[0054] Specifically:

[0055] Medical staff installed the urine drainage control and urine volume measurement device on the patient's bed, via hooks on the mother bag 101 and the first daughter bag 102. Figure 1 (Not marked) It was hung on the edge of the bed and a catheter was inserted into the patient through a urinary catheter.

[0056] Then, power is supplied to the controller 104, and the controller 104 is allowed to operate stably and the first sub-bag 102 is receiving the patient's urine normally.

[0057] It should be noted that:

[0058] The core of the controller 104 is a PCB circuit board. The excitation source unit, signal amplification unit, digitization unit and central processing unit are all packaged on the controller 104. At the same time, the controller 104 is set in a sealed plastic shell.

[0059] like Figure 2 As shown in Part B, the core component of the excitation source unit is the NE555 chip, such as... Figure 2 As shown in section C, the core component of the signal amplification unit is the AD620 chip, such as... Figure 2 As shown in section D, the core component of the digitization unit is the ADC0832 chip, and as shown in section D... Figure 2 As shown in section E, the core component of the central processing unit is the MSPM0C1104 chip, in which,

[0060] Pins 4 and 8 of the NE555 chip are connected to the power supply. Pin 2 is connected to ground via series resistors R1 and R2. Pin 7 is connected to ground via series resistor R2. Pin 6 is connected to ground via series resistors R1 and R2. Pin 5 is connected to ground via series capacitor C1. Pin 1 is connected to ground. Pin 3 outputs a reference AC square wave signal.

[0061] The first capacitive sensor 103 (Cx1) measures the urine flow rate in the urinary catheter based on a reference AC square wave signal to generate a real-time urine flow electrical signal.

[0062] Pin 2 of the AD620 chip receives the real-time urine flow electrical signal, pin 4 is connected to ground, resistor R3 is connected in series between pins 1 and 8, pin 7 is connected to power, pin 6 outputs the amplified real-time urine flow electrical signal, and pin 5 is connected to ground.

[0063] Pin 2 of the ADC0832 chip receives the amplified real-time urine flow electrical signal, pin 3 is idle, pin 4 is connected to ground, pin 6 outputs the digitized real-time urine flow electrical signal, and pin 8 is connected to ground.

[0064] Pin 4 of the MSPM0C1104 chip receives the digitized real-time urine flow electrical signal. Pin 5 is connected to ground via a series resistor R4 and capacitor C2. The series resistor R4 is connected to the power supply. Pin 6 is connected to the power supply. Pin 7 is connected to ground. Pin 8 is connected to pin 1 of the ADC0832 chip. Pin 9 is connected to pin 7 of the ADC0832 chip. Pin 10 is connected to pin 5 of the ADC0832 chip. Pins 11 to 18 are idle.

[0065] In one embodiment of the present invention:

[0066] like Figure 3 As shown, controller 104 is also equipped with:

[0067] The reference capacitor, together with the first capacitive sensor 103, forms a bridge circuit and outputs a differential form of real-time urine flow electrical signal.

[0068] The central processing unit calculates the total urine volume based on the digitized real-time urine flow electrical signal according to the following formula: ,in, This represents the total urine volume. To correct the parameters, For the first capacitive sensor 103 in the first Real-time urine flow electrical signal generated in each sampling period This is the preset frequency.

[0069] Specifically:

[0070] The bridge circuit composed of the reference capacitor and the first capacitor sensor 103 can significantly reduce the temperature drift or error of the first capacitor sensor 103, thereby making its urine measurement more accurate.

[0071] It should be noted that:

[0072] Pin 3 of the NE555 chip is connected in series with the first capacitive sensor 103 (Cx1) and resistor R5 to ground. Pin 3 of the NE555 chip is connected in series with the reference capacitor Cref and resistor R6 to ground. The connection between the first capacitive sensor 103 (Cx1) and resistor R5 is connected to pin 2 of the AD620 chip. The connection between the reference capacitor Cref and resistor R6 is connected to pin 3 of the AD620 chip.

[0073] For the remaining technical details of this embodiment, please refer to the above embodiments, and they will not be repeated here.

[0074] In one embodiment of the present invention:

[0075] like Figure 1 As shown, it also includes:

[0076] Second sub-bag 105;

[0077] The second capacitive sensor 106 is disposed on the second sub-bag 105;

[0078] The urinary catheter is arranged in a Z-shape on the second sub-bag 105, and the second capacitive sensor 106 is arranged on all the urinary catheters. It measures the urine flow rate in the urinary catheter based on the reference AC square wave signal to generate a reference urine flow rate electrical signal.

[0079] The central processing unit calculates the total urine volume based on the digitized real-time urine flow electrical signal according to the following formula: ,in, This represents the capacitance value of the urinary catheter when it is empty. The reference urine flow electrical signal generated by the second capacitive sensor 106.

[0080] Specifically:

[0081] In actual use, the concentration of the patient's urine changes, and these changes are reflected in the measurement value of the first capacitive sensor 103 (Cx1). That is, the real-time urine flow electrical signal output by the first capacitive sensor 103 (Cx1) cannot completely and accurately reflect the patient's total urine volume. Therefore, in this embodiment, a second sub-bag 105 is introduced, and the urine inlet catheter is set in a Z-shape on the second sub-bag 105. In this way, there will be a section in the middle of the urine inlet catheter that is always full of urine. The second capacitive sensor 106 (Cx2) is set here to measure the reference urine flow electrical signal, and the total urine volume value can be obtained by the calculation of the central processing unit.

[0082] It should be noted that:

[0083] like Figure 2 As shown in section A, the two pins of the second capacitive sensor 106 (Cx2) are connected to the power supply and pin 20 of the MSPM0C1104 chip, respectively.

[0084] For the remaining technical details of this embodiment, please refer to the above embodiments, and they will not be repeated here.

[0085] In one embodiment of the present invention:

[0086] The central processing unit outputs an alarm signal according to the following steps:

[0087] S1: Generate real-time urine flow electrical signal The time series;

[0088] S2: Real-time urine flow electrical signal based on the current moment Calculate the electrical signal of real-time urine flow rate compared to the previous moment. and the electrical signal of real-time urine flow at the next moment instantaneous rate of change and ;

[0089] If instantaneous rate of change If the signs are opposite and the absolute values ​​both exceed the first preset threshold, an alarm signal is output.

[0090] S3: If the instantaneous rate of change If the threshold is exceeded and remains so for a first preset time, an alarm signal will be output.

[0091] Or if the instantaneous rate of change If the value is less than the third preset threshold and continues for the second preset time, an alarm signal will be output.

[0092] Specifically:

[0093] In actual use, ideally, the patient's urine should pass through the urinary catheter. However, if other unexpected factors prevent normal urination, especially if the patient's internal organs are diseased, resulting in blood or other fluids mixed in the urine, it is necessary to detect the abnormality in time.

[0094] It should be noted that:

[0095] If other substances are mixed in with the urine, the measured capacitance value will change significantly when it passes through the first capacitance sensor 103 (Cx1), which is the real-time urine flow electrical signal. Significant changes have occurred;

[0096] If the dielectric constant of other substances is greater than that of urine, then when they approach the first capacitance sensor 103 (Cx1), the real-time urine flow electrical signal measured by the first capacitance sensor 103 (Cx1) will be affected. Increase, until the real-time urine flow electrical signal measured by the first capacitive sensor 103 (Cx1) is obtained. Maximum, the real-time urine flow electrical signal measured at the first capacitive sensor 103 (Cx1) The decrease is reflected in the real-time urine flow electrical signal at the current moment. Real-time urine flow electrical signal at the previous moment and the electrical signal of real-time urine flow at the next moment That is, instantaneous rate of change Increasing and positive, instantaneous rate of change Decrease and become negative;

[0097] If the dielectric constant of other substances is less than that of urine, then when they approach the first capacitance sensor 103 (Cx1), the real-time urine flow electrical signal measured by the first capacitance sensor 103 (Cx1) will be affected. The flow rate decreases until it reaches the real-time urine flow electrical signal measured by the first capacitive sensor 103 (Cx1). Minimum, the real-time urine flow electrical signal measured at the distance from the first capacitive sensor 103 (Cx1) Increase, reflected in the real-time urine flow electrical signal at the current moment. Real-time urine flow electrical signal at the previous moment and the electrical signal of real-time urine flow at the next moment That is, instantaneous rate of change Decreasing and negative, instantaneous rate of change Increases and is a positive value;

[0098] In addition, it should be noted that:

[0099] If the urinary catheter is accidentally dislodged or blocked, the lack of urine in the catheter will cause an increase in the measured capacitance value of the first capacitance sensor 103 (Cx1), which corresponds to the real-time urine flow electrical signal. Increase, that is, the instantaneous rate of change Exceeding the second preset threshold and continuing for the first preset time;

[0100] In addition, it should be noted that:

[0101] For the first capacitance sensor 103 (Cx1), the decrease in the measured capacitance value, which is the real-time urine flow electrical signal, is the cause. Decrease, that is, instantaneous rate of change Less than the third preset threshold and lasting for the second preset time;

[0102] In all the above situations, pin 19 of the MSPM0C1104 chip outputs an alarm signal to alert medical personnel to intervene immediately.

[0103] For the remaining technical details of this embodiment, please refer to the above embodiments, and they will not be repeated here.

[0104] In one embodiment of the present invention:

[0105] like Figure 4 As shown, controller 104 is also equipped with:

[0106] The communication unit uploads the total urine volume value to the cloud.

[0107] The clock unit provides the clock frequency for the communication unit.

[0108] Specifically:

[0109] The MSPM0C1104 chip outputs an alarm signal from pin 19, which is transmitted to the hospital's medical monitoring system via the communication unit. At the same time, the clock unit provides the clock frequency for the communication unit.

[0110] It should be noted that:

[0111] like Figure 4 As shown in section F, the core components of the communication unit are the AC6328A2 chip and the ANT3216 communication antenna, as follows: Figure 4 As shown in section G, the core component of the clock unit is a 32MHz crystal oscillator X1;

[0112] Pin 1 of the AC6328A2 chip is connected to the power supply, pin 2 is connected to pin 20 of the MSPM0C1104 chip, pin 3 is connected to the ground, pin 4 is connected in series with resistor R7 to pin 19 of the MSPM0C1104 chip and the ANT3216 communication antenna respectively, and pins 7 and 8 are connected to the USB interface.

[0113] The two pins of the 32MHz crystal oscillator X1 are connected to pins 5 and 6 of the AC6328A2 chip, respectively, and capacitors C3 and C4 are connected in parallel to the two pins of the 32MHz crystal oscillator X1.

[0114] For the remaining technical details of this embodiment, please refer to the above embodiments, and they will not be repeated here.

[0115] In summary, the urine drainage control and urine volume measurement device disclosed in this invention can improve the measurement accuracy of urine volume, accurately capture urine trickle, and effectively protect the patient's clinical treatment.

[0116] Although embodiments of the present invention have been shown and described above, it is understood that the above embodiments are exemplary and should not be construed as limiting the present invention. Those skilled in the art can make changes, modifications, substitutions and variations to the above embodiments within the scope of the present invention.

Claims

1. A urine drainage control and urine volume measurement device, characterized in that, include: The mother bag is equipped with a urine outlet; The first sub-bag is provided with a urination outlet, a urination inlet and a urination tube, and is located on the mother bag and communicates with the mother bag; A first capacitive sensor is disposed on the urine inlet catheter; The controller is configured with: The excitation source unit outputs a reference AC square wave signal based on a preset frequency. The first capacitive sensor measures the urine flow rate in the urinary catheter based on the reference AC square wave signal to generate a real-time urine flow electrical signal. A signal amplification unit receives the real-time urine flow electrical signal and amplifies it to output the amplified real-time urine flow electrical signal. A digitization unit receives the amplified real-time urine flow electrical signal and digitizes it to output the digitized real-time urine flow electrical signal. The central processing unit receives the digitized real-time urine flow electrical signal and calculates the total urine volume based on the digitized real-time urine flow electrical signal.

2. The urine drainage control and urine volume measurement device as described in claim 1, characterized in that, The controller is further provided with: A reference capacitor, together with the first capacitive sensor, forms a bridge circuit and outputs a differential form of the real-time urine flow electrical signal.

3. The urine drainage control and urine volume measurement device as described in claim 2, characterized in that, The central processing unit calculates the total urine volume based on the digitized real-time urine flow electrical signal according to the following formula: ,in, The total urine volume is [the amount of urine produced]. To correct the parameters, For the first capacitive sensor in the first Real-time urine flow electrical signal generated in each sampling period The preset frequency.

4. The urine drainage control and urine volume measurement device as described in claim 3, characterized in that, Also includes: Second sub-bag; A second capacitive sensor is disposed on the second sub-bag; The urinary catheter is arranged in a Z-shape on the second sub-bag, and the second capacitive sensor is arranged on the urinary catheter. The sensor measures the urine flow rate in the urinary catheter based on the reference AC square wave signal to generate a reference urine flow rate electrical signal.

5. The urine drainage control and urine volume measurement device as described in claim 4, characterized in that, Also includes: The central processing unit calculates the total urine volume based on the digitized real-time urine flow electrical signal according to the following formula: ,in, This refers to the capacitance value of the urine inlet catheter in an empty state. The reference urine flow electrical signal generated by the second capacitive sensor.

6. The urine drainage control and urine volume measurement device as described in claim 5, characterized in that, The central processing unit outputs an alarm signal according to the following steps: S1: Generate the real-time urine flow electrical signal The time series; S2: Based on the real-time urine flow electrical signal at the current moment Calculate the electrical signal of the real-time urine flow rate compared to the previous time step. and the real-time urine flow electrical signal at the next moment instantaneous rate of change and ; If the instantaneous rate of change If the signs are opposite and the absolute values ​​both exceed the first preset threshold, then the alarm signal is output.

7. The urine drainage control and urine volume metering device as described in claim 6, characterized in that, The central processing unit also outputs an alarm signal according to the following steps: S3: If the instantaneous rate of change If the second preset threshold is exceeded and continues for a first preset time, the alarm signal is output. Or if the instantaneous rate of change If the value is less than the third preset threshold and remains below the second preset time, then the alarm signal is output.

8. The urine drainage control and urine volume measurement device as described in claim 1, characterized in that, The controller is further provided with: The communication unit uploads the total urine volume value to the cloud; A clock unit that provides a clock frequency for the communication unit.

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