A portable urodynamic detection device

Abstract

The present invention relates to a portable urodynamic detection device, which includes a liquid inlet module, a liquid guiding module, a pressure sensor module, a strain sensor module, a processing circuit module and a display module; the liquid inlet module is funnel-shaped, the liquid outlet end is connected to the liquid guiding module, the pressure sensor module is arranged on the inner wall of the liquid guiding module, the strain sensor module is arranged at the outlet position at the bottom of the liquid guiding module, the input end of the processing circuit module is connected to the pressure sensor module and the strain sensor module, and the output end of the processing circuit module outputs a urine flow rate signal to the display module. Compared with the prior art, the present invention breaks through the previous weighing-type and split-type urine flow rate detection concepts, can not only overcome the disadvantages of the traditional urine flow rate meter such as non-compact structure, difficulty in carrying and home use, but also can achieve high measurement accuracy under portable operation, and is used for dynamic and real-time monitoring of urine flow rate.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to a portable urodynamic detection device. Background Art

[0002] Uroflowmetry is a very commonly used examination item in clinical practice. It can quickly, non-invasively and objectively reflect the micturition function of the examined person. By analyzing parameters such as urine flow velocity, urine flow time and urine volume, a preliminary judgment can be made on whether micturition is normal, which has important diagnostic value and treatment guiding significance in clinical practice.

[0003] Currently, almost all the uroflowmetry detection devices widely used in clinical practice adopt the "weighing method", which requires three major components: a funnel-shaped liquid channel, a urine collection pot and a gravity sensor base. During the examination, the patient is instructed to urinate into the funnel, and the urine is drained through the channel into the urine collection pot. The change in the weight of the urine in the container is monitored in real time by the gravity sensor at the bottom of the latter to obtain the uroflowmetry curve of the examined person for clinical analysis.

[0004] Although the above method has been clinically applied for decades, there are still many technical defects. The most important one is that the device is of a split design and is only suitable for use in a hospital examination room. It is not easy to carry and use at home. For a considerable number of patients who need to perform multiple dynamic micturition monitoring every day, measurement cannot be carried out. Although there are a few small-sized uroflowmetry devices suitable for home use on the market at present, their essence is still a weighing and split design, and it is difficult for the examined person to achieve homogeneous and standardized detection in daily life. In addition, inconsistent micturition heights, easy splashing of urine and interference from artificial artifacts occur from time to time, resulting in difficult-to-interpret results. The most crucial point is that due to the non-compact and bulky structure of the traditional uroflowmetry instrument, patients generally can only urinate in the ward, and the measurement result of uroflowmetry may be inaccurate due to the psychological factors of the patients. Summary of the Invention

[0005] The purpose of the present invention is to provide a portable urodynamic detection device for measuring uroflowmetry at any time.

[0006] The purpose of the present invention can be achieved through the following technical solutions: A portable urodynamic detection device includes a liquid inlet module, a liquid guiding module, a pressure sensor module, a strain sensor module, a processing circuit module and a display module;

[0007] The liquid inlet module is funnel-shaped, and its liquid outlet end is connected to the liquid guiding module. The pressure sensor module is arranged on the inner wall of the liquid guiding module and is used to obtain the pressure signal of urine on the tube wall of the liquid guiding module in real time. The strain sensor module is arranged at the outlet position at the bottom of the liquid guiding module and undergoes strain due to the impact of urine on the strain sensor, and monitors the impact strain of urine on the strain sensor module in real time. The input end of the processing circuit module is connected to the pressure sensor module and the strain sensor module, and is used to process the signal values output by the pressure sensor module and the strain sensor module into a urine flow rate signal value. The output end of the processing circuit module outputs the urine flow rate signal to the display module.

[0008] Preferably, the liquid guiding module is a liquid guiding tube made of rigid material.

[0009] Preferably, the pressure sensor used in the pressure sensor module is a flexible pressure sensor. The pressure sensor is preferably a piezoresistive flexible pressure sensor.

[0010] More preferably, the pressure sensor module includes a voltage division circuit for detecting the change in the resistance value of the piezoresistive flexible pressure sensor.

[0011] Even more preferably, the pressure sensor module includes a signal amplification circuit for amplifying the voltage signal output by the voltage division circuit.

[0012] Preferably, the pressure sensor module integrates three parts: a piezoresistive flexible pressure sensor, a voltage division circuit, and an amplification circuit, and is attached to the inner wall of the liquid guiding module to convert the pressure signal into a voltage signal and further output the voltage signal.

[0013] Preferably, through holes are formed on the side wall of the liquid guiding module for the transmission line connecting the pressure sensor module and the processing circuit module to pass through.

[0014] Preferably, a flexible hydrophobic baffle is used in the strain sensor module for being impacted by urine flow.

[0015] More preferably, the strain sensor used in the strain sensor module is a resistive strain gauge.

[0016] Even more preferably, the strain sensor module includes a direct current bridge for detecting the change in the resistance value of the resistive strain gauge due to the impact of urine flow.

[0017] More preferably, the strain sensor module includes a signal amplification circuit for amplifying the voltage signal output by the direct current bridge.

[0018] Preferably, the strain sensor module is composed of a flexible hydrophobic baffle, a resistive strain gauge, a DC bridge, and an amplifier circuit, and is fixed at the bottom outlet of the liquid guiding module to convert the strain signal of the resistive strain gauge into a voltage signal and further output the voltage signal.

[0019] More preferably, the resistive strain gauge is attached to the flexible hydrophobic baffle.

[0020] Preferably, the distance between the pressure sensor module and the strain sensor module is compact, and the distance range is 0 to 1 cm. The strain sensor module is arranged at the bottom outlet of the liquid guiding module, and the pressure sensor module is arranged on the inner wall of the liquid guiding module at a distance of 0 to 1 cm from the bottom of the liquid guiding module.

[0021] Preferably, the processing circuit module is fixed on the outside of the liquid inlet module.

[0022] Preferably, the processing circuit module includes an A / D conversion circuit, a urine flow rate calculation circuit, and a wireless transmission circuit connected in sequence. The input end of the A / D conversion circuit is connected to the pressure sensor module and the strain sensor module. The urine flow rate calculation circuit calculates the urine flow rate, and the wireless transmission circuit wirelessly transmits the urine flow rate signal to the display module.

[0023] More preferably, the display module includes a display screen for displaying the urine flow rate detection result.

[0024] More preferably, the A / D conversion circuit, the urine flow rate calculation circuit, and the wireless transmission circuit are integrated on a circuit board, and the circuit board is attached to the outer wall of the liquid inlet module.

[0025] Preferably, the urodynamic detection device further includes a power supply for powering the pressure sensor module and the strain sensor module and a power supply for powering the processing circuit module.

[0026] More preferably, the power supply is a battery.

[0027] The present invention uses a novel method: using a flexible pressure sensor and a strain sensor to replace the weighing sensor to measure the urine flow rate.

[0028] When urine enters the liquid guiding module through the liquid inlet module, the urine will flow along the inner wall of the liquid guiding module. The urine flowing through the pressure sensor module will generate a pressure on the pressure sensor. This pressure is proportional to the gravity of the urine flowing through the pressure sensor module. Since urine is incompressible, the pressure of this section of urine on the pressure sensor is proportional to the instantaneous cross-sectional area of the urine flowing through the pressure sensor module. The cross-sectional area of the urine flow section can be obtained by converting the pressure value received by the piezoresistive flexible pressure sensor;

[0029] Meanwhile, a strain sensor module is provided at a position close to the pressure sensor module at the bottom of the liquid guiding module. When the flexible hydrophobic baffle on the strain sensor module is impacted by urine flow, it will undergo elastic bending. There is a one-to-one correspondence between the bending degree of the baffle after being impacted and the flow velocity of the water flow. The flow velocity of the urine flow segment can be obtained by converting the strain received by the resistive strain gauge attached to the flexible hydrophobic baffle.

[0030] Both the pressure sensor module and the strain sensor module are arranged near the bottom outlet of the liquid guiding module, and the pressure sensor module and the strain sensor module are very close to each other. Therefore, the cross-sectional area of the urine flow measured by the pressure sensor module and the flow velocity of the urine measured by the strain sensor module at the same time can be considered as the cross-sectional area and flow velocity of the same urine flow segment currently flowing. The flow rate of this urine flow segment can be calculated as follows:

[0031] Q = S × V

[0032] In the formula, Q is the urine flow rate at the current time point, S is the instantaneous cross-sectional area of the water flow passing through the pressure sensor module, and V is the velocity of the water flow passing through the pressure sensor module.

[0033] The design of the present invention completely breaks through the traditional concept, and uses the wall-attached flexible material micro sensor and the strain sensor to jointly measure the urine flow rate. It is small in size, easy to carry and suitable for home use, and at the same time has high detection accuracy to meet the dynamic and real-time monitoring of the urine flow rate.

[0034] Compared with the prior art, the present invention has the following advantages:

[0035] 1. Through the cooperative design of the pressure sensor module and the strain sensor module on the liquid guiding module, the present invention can respectively obtain the pressure signal of the urine on the tube wall of the liquid guiding module and the impact strain of the urine on the strain sensor module in real time, and obtain the urine flow rate signal value through the processing of the processing circuit module and output it for display. The structure is simple and portable, and patients can use it privately, which helps patients urinate in a relaxed state and can avoid interference from embarrassing psychological factors of patients.

[0036] 2. The present invention breaks through the previous weighing type and split type urine flow rate detection concepts. It can not only overcome the disadvantages of the traditional urine flow rate meter such as non-compact structure, difficulty in carrying and home use, but also achieve high measurement accuracy under portable operation for dynamic and real-time monitoring of the urine flow rate.

[0037] 3. The present invention applies a flexible pressure sensor to the problem of measuring the weight of the urine flow segment. By measuring the weight of the urine flow segment flowing through the pressure sensor, the cross-sectional area of the urine flow segment can be obtained. The flexible pressure sensor has more significant sensitivity and accuracy compared to general pressure sensor modules. Combining the flexible hydrophobic baffle and the strain gauge to measure the urine flow velocity, and with the help of an integrated circuit module (processing circuit), an integrated design of a uroflowmeter can be achieved. The structure is simple, compact, and lightweight, and is very suitable for home self-testing of uroflowmetry.

[0038] 4. Through the cooperative design of the liquid inlet module, liquid guiding module, pressure sensor module, and strain sensor module, the present invention is reliable in use, has a simple manufacturing method, and the cost of the required key components is low, making it suitable for mass production.

[0039] 5. The device of the present invention can be combined with the Internet to achieve remote medical diagnosis and is suitable for home self-testing of uroflowmetry.

[0040] 6. The instrument of the present invention is small in volume and compact in structure. Patients can carry it with them, and it is very convenient to measure uroflowmetry. Compared with traditional and mainstream weighing-type uroflowmetry instruments, the present invention can measure the real-time uroflow rate only by installing a flexible pressure sensor module and a strain-type sensor module at the liquid guiding module. Compared with traditional weighing-type uroflowmetry instruments that require carrying a weighing base, it is more lightweight and portable.

[0041] 7. The instrument of the present invention consumes very little power during operation, and only a battery is required for power supply, which is more conducive to carrying it with you at any time to measure uroflowmetry. BRIEF DESCRIPTION OF THE DRAWINGS

[0042] Figure 1 is a schematic structural diagram of the detection device of the present invention;

[0043] Figure 2 is a front view of the detection device of the present invention;

[0044] Figure 3 is an enlarged view of the bottom of the detection device of the present invention;

[0045] Figure 4 is a working principle diagram of the detection device of the present invention;

[0046] Figure 5 is a schematic diagram of the piezoresistive flexible pressure sensor of the detection device of the present invention;

[0047] Figure 6 is a piezoresistive relationship curve graph of the piezoresistive flexible pressure sensor of the detection device of the present invention;

[0048] Figure 7 is a force analysis diagram of the pressure of the urine flow on the liquid guiding tube of the detection device of the present invention;

[0049] Figure 8Force analysis diagram of the strain sensor module of the detection device of the present invention under the impact of urine flow;

[0050] Figure 9 Side view of the force analysis of the strain sensor module of the detection device of the present invention under the impact of urine flow;

[0051] In the figure: 1 - liquid inlet module, 2 - liquid guiding module, 3 - pressure sensor module, 4 - strain sensor module, 41 - flexible hydrophobic baffle, 42 - resistive strain gauge, 5 - processing circuit module, 51 - A / D conversion circuit, 52 - urine flow rate calculation circuit, 53 - wireless transmission circuit, 6 - display module, 7 - through hole, 8 - transmission line. Specific embodiments

[0052] The present invention will be described in detail below with reference to the accompanying drawings and specific embodiments. The following embodiments are implemented on the premise of the technical solution of the present invention, and the detailed implementation manners and specific operation processes are given, but the protection scope of the present invention is not limited to the following embodiments.

[0053] Embodiment 1

[0054] A portable urodynamic detection device, as Figures 1 to 3 shown, includes a liquid inlet module 1, a liquid guiding module 2, a pressure sensor module 3, a strain sensor module 4, a processing circuit module 5 and a display module 6. The liquid inlet module 1 is funnel-shaped, the upper end of the liquid guiding module 2 is connected to the lower end of the liquid inlet module 1, the pressure sensor module 3 is arranged on the inner wall of the liquid guiding module 2 for obtaining the pressure signal of urine on the pipe wall in real time, the pressure sensor module 3 is connected to the processing circuit module 5, the strain sensor module 4 has a flexible hydrophobic baffle 41 and a resistive strain gauge 42 attached to the flexible hydrophobic baffle 41, the strain sensor module 4 is arranged at the bottom outlet of the liquid guiding module 2 for obtaining the impact signal of urine with different flow rates on the flexible hydrophobic baffle 41 in real time, the strain sensor module 4 is connected to the processing circuit module 5, and the processing circuit module 5 processes the signal values output by the pressure sensor module 3 and the strain sensor module 4 into urine flow rate signal values and transmits the urine flow rate signal to the display module 6 through the output end.

[0055] In this embodiment, the pressure sensor module 3 is directly arranged in the liquid guiding module 2 through which urine flows to detect the pressure signal of the liquid on the pipe wall of the liquid guiding pipe at different flow rates. The strain sensor module 4 is arranged at the bottom outlet of the liquid guiding module 2 for obtaining the impact signal of urine with different flow rates on the flexible hydrophobic baffle 41 in real time, and the pressure signal and the impact signal are converted into urine flow rate by the processing circuit module 5. The design of the present invention completely breaks through the previous weighing type and split type urine flow rate detection concepts, and can not only overcome the disadvantages of the traditional urine flow rate meter such as non-compact structure, difficult to carry and use at home, but also achieve high measurement accuracy under portable operation.

[0056] Example 2

[0057] A portable urodynamic detection device, comprising: a liquid inlet module 1, a liquid guiding module 2, a pressure sensor module 3, a strain sensor module 4, a flexible hydrophobic baffle 41, a resistive strain gauge 42, a processing circuit module 5, an A / D conversion circuit 51, a urine flow rate calculation circuit 52, a wireless transmission circuit 53, a power supply and a display module 6; the liquid inlet module 1 is designed in a funnel shape; the upper end of the liquid guiding module 2 is connected to the liquid inlet end;

[0058] As Figure 4 shown, the pressure sensor module 3 includes a flexible pressure sensor R, and the flexible pressure sensor R is connected in a DC voltage dividing circuit. When the flexible pressure sensor R is not under pressure:

[0059] R = R0

[0060] ΔR = 0

[0061] where R0 is the voltage dividing resistor, and the value of R0 is equal to the resistance value of the piezoresistive flexible pressure sensor R when it is not under pressure. When the flexible pressure sensor R is under the pressure of the urine flow segment, the resistance value will decrease, and a resistance change ΔR will occur. This resistance change ΔR will be manifested as a decrease in the voltage U I across the flexible pressure sensor, and the voltage U I is amplified by the subsequent operational amplifier circuit, and the cross-sectional area of the current urine flow segment can be obtained through conversion by the processing circuit module 5;

[0062] As Figure 4 shown, the strain sensor module 4 includes a resistive strain gauge R s , and the resistive strain gauge R s is connected in a DC bridge. When the flexible hydrophobic baffle is not impacted by water flow, the bridge is in balance:

[0063] R s = R1 = R2 = R3

[0064] U1 = 0

[0065] When the flexible hydrophobic baffle is impacted by water flow, the resistive strain gauge attached to the flexible hydrophobic baffle will generate a resistance change ΔR s This resistance change ΔR s will be manifested as a non-zero output voltage value U1 of the DC bridge. The voltage U1 is amplified by the subsequent operational amplifier circuit, and the velocity of the current urine flow segment can be obtained through conversion by the processing circuit module 5.

[0066] The pressure sensor module 3 and the strain sensor module 4 convert the pressure signals and strain signals obtained when passing through urine segments with different cross-sectional areas and different flow rates into voltage signals and further transmit them to the A / D conversion circuit 51; after the voltage signals are A / D converted, they are sent to the urine flow rate calculation circuit 52 for signal processing, and the processed urine flow rate signals are transmitted to the display module 6 through the wireless transmission circuit 53 to display the detection results. The power supply powers the A / D conversion circuit 51, the urine flow rate calculation circuit 52, and the wireless transmission circuit 53. The above circuits are integrated on a circuit board.

[0067] Embodiment 3

[0068] A portable urodynamic detection device, as Figure 1 shown, includes:

[0069] The liquid inlet module 1 for receiving urine. In order to effectively receive urine, the liquid inlet module is made into a funnel shape so that urine can flow into the liquid guiding module 2. The liquid inlet module 1 can be made of non-absorbent materials such as glass or plastic;

[0070] The liquid guiding module 2 for urine to flow through. A through hole 7 is opened at the position of the pressure sensor module 3 at the bottom of the liquid guiding module 2, as Figure 3 shown, so that the transmission line 8 connecting the pressure sensor module 3 and the processing circuit module 5 can pass through smoothly. In order to enable the pressure sensor module 3 attached to the inner wall of the liquid guiding module 2 to accurately detect the pressure of the liquid on the inner wall of the liquid guiding module, the base of the pressure sensor module 3 - the liquid guiding module 2 should be made of rigid materials, such as stainless steel or glass.

[0071] The flexible pressure sensor module 3 for detecting the pressure of the liquid on the pipe wall. By attaching the flexible pressure sensor to the inner wall of the liquid guiding module 2, when urine flows from the liquid inlet module 1 through the liquid guiding module 2, the liquid will generate pressure on the inner wall of the liquid guiding module 2, and the pressure sensor module 3 can detect this pressure value, generating a change in resistance value ΔR and converting it into the voltage value of the bridge circuit where the pressure sensor is located. As Figure 4 explains the working principle of the pressure sensor module. The reason for selecting the piezoresistive flexible pressure sensor (such as Figure 5 ) is that the piezoresistive flexible pressure sensor can detect static force, is particularly suitable for detecting the pressure of water flow on the pipeline; has high sensitivity; low energy consumption; and high response repeatability.

[0072] The strain sensor module 4 for detecting the liquid flow rate. By fixing the flexible hydrophobic baffle 41 at the bottom of the outlet of the liquid guiding module 2 and attaching the resistive strain gauge 42 on the flexible hydrophobic baffle 41, when urine flows out of the liquid guiding module 2 from the liquid inlet module 1, the liquid will impact the flexible hydrophobic baffle 41, causing the flexible hydrophobic baffle 41 to undergo elastic deformation, resulting in the resistive strain gauge 42 undergoing strain and generating a change in resistance value ΔRs , and convert ΔR s into the voltage value U1 of the bridge circuit where the resistive strain gauge is located. As Figure 4 explains the working principle of the strain sensor module.

[0073] The working process of this example is described in detail below:

[0074] (1) When urine enters the liquid guide module through the liquid inlet module, the urine will flow along the inner wall of the liquid guide module. The urine flowing through this section of the pressure sensor module 3 will exert a pressure on the pressure sensor module 3. This pressure is proportional to the gravity of the urine flowing through this section of the pressure sensor module 3. As Figure 7 shown, the following relationship is satisfied:

[0075] F = Δmgcosθ

[0076] where F is the pressure of the urine flow segment received by the pressure sensor, Δm is the instantaneous mass of the urine flow segment currently flowing through the pressure sensor, g is the acceleration due to gravity, and θ is the inclination angle of the liquid guide module 2. The urine is incompressible, and the instantaneous mass of the urine flow segment currently flowing through the pressure sensor module 3 is proportional to the instantaneous cross-sectional area S of the urine flow segment currently flowing through the pressure sensor:

[0077] Δm = kS

[0078] where k is a proportionality constant that can be measured through experiments, and S is the instantaneous cross-sectional area of the urine flow segment currently flowing through the pressure sensor. Therefore:

[0079] F = kSgcosθ

[0080] The relationship between the pressure F of the urine flow segment received by the pressure sensor module 3 and the resistance value R of the pressure sensor conforms to Figure 6 the piezoresistive characteristic curve of the piezoresistive flexible pressure sensor. Therefore, when the pressure sensor is subjected to the pressure of the urine flow segment, the resistance value R changes. As Figure 4 shown, the voltage division circuit of the pressure sensor module 3 converts the change in the resistance value R into a change in the voltage value U I , and the voltage value U I output by the amplifier circuit satisfies:

[0081]

[0082] As Figure 4 shown, the amplified voltage U o is sampled by the A / D conversion circuit 51 and then converted into a digital signal and given to the urine flow rate calculation circuit 52. The urine flow rate calculation circuit 52 obtains the value of the voltage U o . According to the above formula, the urine flow rate calculation circuit 52 inversely calculates the resistance value R of the piezoresistive flexible pressure sensor:

[0083]

[0084] The urine flow rate calculation circuit 52 obtains the magnitude of the urine flow segment pressure value F received by the pressure sensor by referring to the piezoresistive characteristic curve based on the calculated resistance value R of the piezoresistive flexible pressure sensor: Figure 6

[0085]

[0086] Then, according to the formula:

[0087] F = kSgcosθ

[0088] the urine flow rate calculation circuit 52 reversely infers the instantaneous cross-sectional area S of the urine flow segment flowing through the pressure sensor at the current time point.

[0089] (2) At the same time, a strain sensor module 4 is provided at the bottom of the liquid guide module 2 close to the pressure sensor module 3. The flexible hydrophobic baffle 41 on the strain sensor module 4 will undergo elastic bending when impacted by the urine flow. There is a one-to-one correspondence between the bending degree of the flexible hydrophobic baffle 41 after being impacted and the flow velocity V of the water flow. The resistive strain gauge 42 is attached to the flexible hydrophobic baffle 41, as Figure 8 、 Figure 9 shown. The strain of the resistive strain gauge 42 satisfies:

[0090]

[0091] where ε is the strain generated by the resistive strain gauge, E is the elastic modulus of the flexible hydrophobic baffle, a and b are the length and width of the flexible hydrophobic baffle, l is the length of the flexible hydrophobic baffle, and q is the unit length impact pressure of the urine flow acting on the flexible hydrophobic baffle;

[0092] It can be obtained that:

[0093]

[0094] According to the momentum theorem, the relationship between the urine segment flow velocity V and q can be obtained:

[0095]

[0096] where ρ is the water flow density;

[0097] Combining the above two formulas, we get:

[0098]

[0099] The relationship between the strain ε and the resistance of the resistive strain gauge is:

[0100] ​

[0101] Where R s is the resistance of the resistive strain gauge, ΔR s is the change in the resistance of the resistive strain gauge, and K s is the sensitivity coefficient of the strain gauge, which is a constant within a certain strain range.

[0102] As Figure 4 shown, the resistive strain gauge R s is installed as one arm of a DC bridge in the DC bridge circuit. R1, R2, and R3 are ordinary fixed-value resistors, which together with R s form a bridge. The balance condition of the bridge is satisfied:

[0103] R s = R1 = R2 = R3

[0104] At this time, the output voltage of the bridge satisfies:

[0105] U1 = 0

[0106] When the flexible piezoresistive pressure sensor R s is subjected to an external pressure and undergoes a change in resistance ΔR s , we get:

[0107]

[0108] Because the change in resistance ΔR s is very small, the above formula can be written as the following formula without affecting the accuracy:

[0109]

[0110] The output voltage U1 of the bridge is amplified by the subsequent amplifier circuit:

[0111]

[0112] Integrating the above formulas, the relationship between U2 and the flow velocity V of the urine flow segment can be obtained:

[0113]

[0114] As Figure 4 shown, the amplified voltage U2 is sampled by the A / D conversion circuit 51 and then converted into a digital signal and given to the urine flow rate calculation circuit 52. The urine flow rate calculation circuit 52 obtains the value of the voltage U2. According to the above formula, the velocity V of the urine flow segment of the impact strain sensor module 4 is obtained.

[0115] (3) The pressure sensor module and the strain sensor module are both arranged near the bottom outlet of the liquid guiding module. The pressure sensor module and the strain sensor module are very close to each other. Therefore, the cross-sectional area S of the urine flow measured by the pressure sensor module and the urine flow velocity V measured by the strain sensor module at the same time can be considered as the cross-sectional area and flow velocity of the same section of urine flow passing through at present. The flow rate Q of this section of urine flow can be calculated as follows:

[0116] Q = S × V

[0117] The flow rate value Q of the urine segment flowing through the pressure sensor module 3 and the strain sensor module 4 is calculated in the processing circuit module 5.

[0118] In actual operation, the voltage signals U o and U2 generated by the pressure sensor module 3 and the strain sensor module 4 can be received by a technically mature single-chip microcomputer to detect the change of this signal. There is a ready-made A / D sampling conversion circuit in the single-chip microcomputer to convert the analog quantity into a digital quantity. Then, a program is written into the single-chip microcomputer to control the single-chip microcomputer to perform real-time operation to determine the urine flow rate obtained at a certain moment. Moreover, the single-chip microcomputer is integrated with wireless transmission modules such as radio frequency and Bluetooth, and can transmit the calculated urine flow rate data to a mobile phone or a computer for further analysis and processing.

[0119] Therefore, it can be seen from the above embodiments that based on the accurate measurement of the urine flow rate, the measuring components of the present invention are a flexible piezoresistive sensor and a resistive strain gauge. The flexible piezoresistive sensor and the resistive strain gauge respectively measure the cross-sectional area and flow velocity of the urine segment. Through the integrated design of the flexible sensor and the liquid guiding tube, the structure of the present invention is simpler and lighter than that of the traditional urine flow rate meter, greatly simplifying the structure of the urine flow rate meter. The invented urine flow rate detection device is more portable than the traditional urine flow rate meter.

[0120] The above description of the embodiments is for those of ordinary skill in the art to understand and use the invention. It is obvious that those skilled in the art can easily make various modifications to these embodiments and apply the general principles described herein to other embodiments without creative labor. Therefore, the present invention is not limited to the above embodiments, and all improvements and modifications made by those skilled in the art without departing from the scope of the present invention should be within the protection scope of the present invention.

Claims

1. A portable urodynamic detection device, characterized in that, It includes a liquid inlet module (1), a liquid guiding module (2), a pressure sensor module (3), a strain sensor module (4), a processing circuit module (5) and a display module (6); The liquid inlet module (1) is funnel-shaped, and its liquid outlet end is connected to the liquid guiding module (2). The pressure sensor module (3) is arranged on the inner wall of the liquid guiding module (2), and the strain sensor module (4) is arranged at the outlet position at the bottom of the liquid guiding module (2). The input end of the processing circuit module (5) is connected to the pressure sensor module (3) and the strain sensor module (4), and the output end of the processing circuit module (5) outputs a urine flow rate signal to the display module (6); The processing circuit module (5) converts the pressure value received by the pressure sensor module (3) to obtain the cross-sectional area of the urine flow segment, and converts the strain received by the strain sensor module (4) to obtain the flow velocity of the urine flow segment. The flow rate of this segment of urine is calculated from the cross-sectional area of the urine flow segment measured by the pressure sensor module (3) and the flow velocity of the urine flow segment measured by the strain sensor module (4) at the same time; The pressure sensor module (3) integrates a piezoresistive flexible pressure sensor, a voltage dividing circuit and an amplifying circuit, and is affixed to the inner wall of the liquid guiding module (2); The strain sensor module (4) consists of a flexible hydrophobic baffle (41), a resistive strain gauge (42), a direct current bridge and an amplifying circuit, and is fixed at the bottom outlet of the liquid guiding module (2); The resistive strain gauge (42) is affixed to the flexible hydrophobic baffle (41); The distance between the pressure sensor module (3) and the strain sensor module (4) is 0 - 1 cm. The strain sensor module (4) is arranged at the bottom outlet of the liquid guiding module (2), and the pressure sensor module (3) is arranged on the inner wall of the liquid guiding module (2) at a distance of 0 - 1 cm from the bottom of the liquid guiding module (2).

2. The portable urodynamic detection device according to claim 1, wherein The liquid guiding module (2) is a liquid guiding tube made of a rigid material.

3. The portable urodynamic detection device according to claim 1, characterized in that, A through hole (7) is opened on the liquid guiding module (2), and the transmission line (8) for connecting the pressure sensor module (3) and the processing circuit module (5) passes through the through hole (7).

4. The portable urodynamic detection device according to claim 1, wherein The processing circuit module (5) includes an A / D conversion circuit (51), a urine flow rate calculation circuit (52) and a wireless transmission circuit (53) connected in sequence. The input end of the A / D conversion circuit (51) is connected to the pressure sensor module (3) and the strain sensor module (4). The urine flow rate calculation circuit (52) calculates the urine flow rate, and the wireless transmission circuit (53) wirelessly transmits the urine flow rate signal to the display module (6).

5. The portable urodynamic detection device according to claim 4, characterized in that The A / D conversion circuit (51), the urine flow rate calculation circuit (52) and the wireless transmission circuit (53) are integrated on a circuit board, and the circuit board is affixed to the outer wall of the liquid inlet module (1).

6. A portable urodynamic detection device according to any one of claims 1 to 5, characterized in that, The urodynamic detection device further includes a power supply for supplying power to the pressure sensor module (3) and the strain sensor module (4) and a power supply for supplying power to the processing circuit module (5).

Images