A body cavity effusion pressure self-adaptive control drainage device

Abstract

The application discloses a kind of body cavity effusion pressure self-adaptive control drainage device, it is related to body cavity effusion technical field, including drainage tube, the top of drainage tube is fixedly connected with three-way joint;Liquid storage bag is connected to the export end of drainage tube;Pinch valve is set on drainage tube;Pressure sensor is set on three-way joint;Driving assembly is drivingly connected with pinch valve;Control box is electrically connected with pressure sensor and driving motor respectively, and control box is internally provided with microprocessor;And valve handle is set on pinch valve;By setting pressure sensor, control box, microprocessor and driving assembly, and control box is electrically connected with pressure sensor and driving motor respectively, while setting the setting panel electrically connected with microprocessor, so that medical staff can preset pressure safety range according to patient type, and pressure sensor monitors body cavity pressure in real time and feeds back to microprocessor.

Description

Technical Field

[0001] This invention relates to the field of body cavity effusion technology, specifically to a body cavity effusion pressure adaptive control drainage device. Background Technology

[0002] Pleural effusion and ascites are common clinical conditions. Large amounts of fluid can compress the heart and lungs, leading to unstable vital signs. In groups sensitive to volume changes, such as fetal hydrops and critically ill patients, the precision and safety requirements for drainage procedures are even higher. Currently, commonly used drainage devices in clinical practice mainly rely on gravity drainage or constant negative pressure suction. Their flow rate control is mostly achieved by manually adjusting the clamp or simple regulating valve, lacking the ability to sense and adjust the body cavity pressure in real time.

[0003] Existing drainage devices have the following drawbacks: their structure typically consists only of a drainage tube and a reservoir, and the opening of the clamp valve must be manually adjusted by medical staff based on experience, failing to automatically adjust the drainage rate according to real-time changes in body cavity pressure. When the body cavity pressure is too high, a slow drainage rate will not effectively relieve the pressure; when the body cavity pressure is too low, a fast drainage rate can easily lead to circulatory instability, decreased blood pressure, or even pulmonary re-expansion edema. This open-loop control method results in a severe disconnect between drainage rate and body cavity pressure, making it difficult to achieve safe and precise drainage management, especially for vulnerable patients such as those with fetal hydrops.

[0004] To address this issue, those skilled in the art have proposed an adaptive control drainage device for body cavity effusion pressure to solve the problems raised in the background art. Summary of the Invention

[0005] The purpose of this invention is to provide a body cavity effusion pressure adaptive control drainage device to solve the problem that existing drainage devices rely solely on drainage tubes, reservoir bags, and manually adjustable clamp valves, which cannot automatically adjust the drainage speed according to real-time changes in body cavity pressure.

[0006] To achieve the above objectives, the present invention provides the following technical solution: a body cavity effusion pressure adaptive control drainage device, comprising a drainage tube, wherein a three-way interface is fixedly connected to the top of the drainage tube;

[0007] A liquid storage bag is connected to the outlet end of the drainage tube;

[0008] A pinch valve is installed on the drainage pipe;

[0009] A pressure sensor is mounted on the three-way connector;

[0010] The drive assembly is connected to the clamp valve via a drive mechanism;

[0011] The control box is electrically connected to the pressure sensor and the drive motor respectively, and a microprocessor is installed inside the control box.

[0012] And a valve handle, which is provided on the pinch valve.

[0013] Preferably, it also includes a setting panel, which is disposed on the control box and electrically connected to the microprocessor.

[0014] Preferably, the inner side of the clamping valve is provided with clamping rollers, and the driving component is a drive motor.

[0015] Preferably, the output end of the drive motor is fixedly connected to a screw sleeve, and the screw sleeve is internally threaded to a screw rod, and the front end of the screw rod is fixedly connected to an arc-shaped push plate, which is connected to the clamping roller.

[0016] Preferably, the drive motor is a stepper motor.

[0017] Preferably, the microprocessor is configured to receive pressure signals collected by a pressure sensor, compare the real-time pressure with the pressure safety range input on the setting panel, and control the drive motor to adjust the opening degree of the pinch valve based on the comparison result.

[0018] Compared with the prior art, the present invention has the following beneficial effects:

[0019] 1. This invention incorporates a pressure sensor, a control box, a microprocessor, and a drive assembly. The control box is electrically connected to both the pressure sensor and the drive motor. A setting panel, also electrically connected to the microprocessor, allows medical personnel to preset a safe pressure range based on patient type. The pressure sensor monitors the body cavity pressure in real time and feeds it back to the microprocessor. The microprocessor automatically controls the drive assembly based on the comparison results, thereby adjusting the opening of the clamp valve. Compared to existing technologies that rely solely on drainage tubes, reservoir bags, and manually adjusted clamp valves, this invention achieves closed-loop control based on real-time feedback of body cavity pressure. It automatically adjusts the drainage rate according to pressure changes, preventing excessively fast or slow drainage from affecting the patient's vital signs and significantly improving the accuracy and safety of drainage.

[0020] 2. This invention configures a microprocessor to receive pressure signals collected by a pressure sensor, compares the real-time pressure with the pressure safety range input on the set panel, and controls the drive motor to adjust the opening degree of the clamp valve based on the comparison result, forming a complete pressure-flow rate closed-loop control logic. This achieves fully automated management of the drainage process, reduces the burden of frequent manual adjustments by medical staff, and effectively prevents complications such as pulmonary re-expansion edema or circulatory failure caused by sudden changes in body cavity pressure. Attached Figure Description

[0021] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this invention. For those skilled in the art, other drawings can be obtained based on these drawings.

[0022] Figure 1 This is a three-dimensional structural diagram of the present invention;

[0023] Figure 2 For the present invention Figure 1 Schematic diagram of the structure of the three-way interface;

[0024] Figure 3 For the present invention Figure 1 A cross-sectional view of the central control box;

[0025] Figure 4 For the present invention Figure 1 A schematic diagram of the drive motor.

[0026] In the picture:

[0027] 1. Drainage tube; 11. Liquid storage bag; 12. T-junction; 13. Valve handle; 14. Pinch valve; 2. Pressure sensor; 21. Drive motor; 22. Connecting wire; 23. Control box; 24. Setting panel; 25. Microprocessor; 26. Pinch roller; 27. Arc-shaped push plate. Detailed Implementation

[0028] To enable those skilled in the art to better understand the technical solution of the present invention, the present invention will be further described in detail below with reference to the accompanying drawings.

[0029] As attached Figure 1 To be continued Figure 4 As shown:

[0030] Example 1: The present invention provides a body cavity effusion pressure adaptive control drainage device, including a drainage tube 1, wherein a three-way interface 12 is fixedly connected to the top of the drainage tube 1;

[0031] A liquid storage bag 11 is connected to the outlet end of the drainage tube 1;

[0032] A pinch valve 14 is provided on the drainage pipe 1;

[0033] Pressure sensor 2 is mounted on the three-way interface 12;

[0034] The drive assembly is connected to the clamp valve 14 in a driving manner;

[0035] The control box 23 is electrically connected to the pressure sensor 2 and the drive motor 21 respectively, and a microprocessor 25 is installed inside the control box 23.

[0036] And valve handle 13, which is disposed on the pinch valve 14.

[0037] During operation, the operator first installs the control box 23 onto the outside of the pinch valve 14, and then electrically connects the pressure sensor 2, drive motor 21, and control box 23 together via connecting wires 22, completing the hardware assembly of the device. The control box 23 uses an IP54-rated waterproof and dustproof housing and integrates power management and signal conditioning circuits. The microprocessor 25 uses an STM32F103C8T6 32-bit ARM Cortex-M3 microcontroller with a working frequency of 72MHz. It has a built-in 12-bit successive approximation ADC, three general-purpose timers, and two watchdog timers to ensure the real-time performance and reliability of the system. Pressure sensor 2 uses an NXPMPXV4006G medical-grade silicon piezoresistive pressure sensor with a range of 0 to 6 kPa (approximately 0 to 60 cmH2O), an operating voltage of 5VDC, an output of 0.2V to 4.7V analog voltage signal, a sensitivity of 1.2mV / kPa, and a full-range accuracy error of no more than ±5%. It has a built-in temperature compensation circuit, which can effectively suppress the influence of ambient temperature on measurement accuracy.

[0038] Through the above setup, the device establishes a complete signal chain from pressure sensing to regulation. The control box 23 provides centralized installation and electrical connection for each electronic component. The microprocessor 25, as the control core, is responsible for data acquisition and decision calculation. The pressure sensor 2 can convert the body cavity pressure into an analog voltage signal that can be recognized by the microprocessor 25 in real time, providing a hardware foundation for subsequent closed-loop control.

[0039] 1. In one embodiment of the present invention, a setting panel 24 is further included, which is disposed on the control box 23 and electrically connected to the microprocessor 25.

[0040] During operation, the operator first installs the setting panel 24 on the upper surface of the control box 23 and electrically connects it to the I / O interface of the microprocessor 25 via an FPC cable. The setting panel 24 uses a 4.3-inch TFT color touchscreen (model: ZLN430A) with a resolution of 480×272, supports the I2C serial communication protocol, and has a built-in GT911 series touch control chip, enabling simultaneous 5-point touch. The setting panel 24 operates at 3.3V, consumes less than 200mW, and has adjustable backlight brightness. The microprocessor 25 communicates with the setting panel 24 via the I2C interface, using polling or interrupt methods to read the user's touch input. When medical personnel touch the numeric input area on the setting panel 24, the microprocessor 25 receives the key value and updates the display in real time. Finally, by confirming the input via the confirmation button, the threshold parameters (the upper and lower limits of the pressure safety range) are stored in the microprocessor 25's internal EEPROM (Electrically Erasable Programmable Read-Only Memory, 2KB in capacity), ensuring that the parameters are not lost even after the device is powered off.

[0041] Through the above settings, the setting panel 24 provides medical staff with an intuitive human-computer interaction interface, supports flexible setting and real-time display of the pressure safety range, and the microprocessor 25 can persistently store the threshold parameters input by the user, so that the device can realize personalized drainage management according to different patient types (such as fetal hydrops, adult pleural effusion, etc.).

[0042] 2. In one embodiment of the present invention, a clamping roller 26 is provided on the inner side of the clamping valve 14, and the driving component is a drive motor 21.

[0043] During operation, the operator installs the clamping roller 26 in the inner guide rail of the clamping valve 14, allowing it to slide freely along the vertical direction of the drainage tube 1 within the valve body. The clamping roller 26 is injection molded from medical-grade polyoxymethylene (POM) material, possessing self-lubricating and wear-resistant properties. Its wheel surface contacts the outer wall of the drainage tube 1, and in conjunction with the arc-shaped push plate 27, it compresses or releases the drainage tube 1. The drive assembly uses a drive motor 21, which is fixed to the housing of the clamping valve 14 via a motor bracket. Its output shaft is connected to the clamping roller 26 via the arc-shaped push plate 27. When the microprocessor 25 sends a control signal, the drive motor 21 receives the pulse signal and generates rotational motion. The arc-shaped push plate 27 converts the rotational motion into linear motion, pushing the clamping roller 26 to move along the guide rail, thereby changing the degree of compression between the clamping roller 26 and the drainage tube 1.

[0044] With the above configuration, the clamp valve 14 and the drive motor 21 constitute a precise electromechanical actuator. The clamp roller 26, as an actuator that directly acts on the drainage tube 1, can convert the rotational motion of the drive motor 21 into continuous adjustment of the squeezing pressure on the drainage tube 1, thereby realizing linear and controllable adjustment of the drainage speed.

[0045] 3. In one embodiment of the present invention, the output end of the drive motor 21 is fixedly connected to a screw sleeve, and the screw sleeve is internally threaded to a screw rod, and the front end of the screw rod is fixedly connected to an arc-shaped push plate 27, and the arc-shaped push plate 27 is connected to the clamping roller 26.

[0046] During operation, the operator secures the output shaft of the drive motor 21 to a threaded sleeve via a coupling. The threaded sleeve is made of brass and has an M4×0.7 trapezoidal internal thread on its inner wall. The screw is made of stainless steel (grade SUS304), with an outer diameter of 4mm and a pitch of 0.7mm. Its surface is polished to reduce the coefficient of friction. The front end of the screw is fixedly connected to an arc-shaped push plate 27 via a threaded connection or integral molding. The arc-shaped push plate 27 is injection molded from medical-grade polycarbonate (PC) material, and its front end face has an arc-shaped groove that matches the outer contour of the clamping roller 26. The arc-shaped push plate 27 and the clamping roller 26 are connected together by a snap-fit ​​connection or abutment. When the microprocessor 25 controls the drive motor 21 to rotate in the forward or reverse direction, the drive motor 21 drives the screw sleeve to rotate. The screw sleeve drives the screw rod to make linear extension and retraction movements along the axial direction through the internal thread. The screw rod drives the arc-shaped push plate 27 to move synchronously. The arc-shaped push plate 27 then pushes or releases the clamping roller 26, changing the squeezing position of the clamping roller 26 on the drainage tube 1.

[0047] With the above configuration, the helical transmission mechanism composed of the screw sleeve, screw and arc-shaped push plate 27 can smoothly convert the rotational motion of the drive motor 21 into linear motion and has a self-locking characteristic (that is, when the drive motor 21 stops rotating, the screw cannot retract on its own under the action of external force), so that the opening of the clamp valve 14 can still be maintained in the power-off state, preventing unexpected changes in the drainage speed and improving the safety and reliability of the device.

[0048] 4. In one embodiment of the present invention, the drive motor 21 is a stepper motor.

[0049] During operation, the operator fixes the stepper motor (model: 28BYJ-48) onto the housing of the clamp valve 14, and its leads are connected to the output terminal of the motor drive circuit (model: ULN2003) via connecting wire 22. This stepper motor is a five-wire, four-phase structure with a step angle of 5.625° and a reduction ratio of 1 / 64. This means that for every 64 pulse signals received by the motor rotor, the output shaft rotates one revolution. Each step of the output shaft rotation (i.e., one pulse signal corresponds to an output shaft rotation angle) corresponds to a linear displacement of approximately 0.011 mm (lead 0.7 mm ÷ 64). A timer channel of the microprocessor 25 is used to generate PWM pulse signals, with a pulse frequency adjustable between 100Hz and 2000Hz and a pulse count configurable between 0 and 8000. When the microprocessor 25 needs to increase the opening of the clamp valve 14, it outputs a positive pulse sequence to the motor drive circuit, causing the stepper motor to rotate forward a specified number of steps; when it needs to decrease the opening of the clamp valve 14, it outputs a reverse pulse sequence, causing the stepper motor to rotate backward a specified number of steps. The angle of the stepper motor output shaft is precisely proportional to the number of input pulses, thus the displacement of the arc-shaped push plate 27 can be precisely controlled.

[0050] 5. In one embodiment of the present invention, the microprocessor 25 is configured to receive the pressure signal collected by the pressure sensor 2, compare the real-time pressure with the pressure safety range input by the setting panel 24, and control the drive motor 21 to adjust the opening degree of the clamp valve 14 according to the comparison result.

[0051] During operation, the operator first inputs the upper limit value P_max and the lower limit value P_min of the pressure safety range via the setting panel 24 (e.g., P_max = -5cmH2O, P_min = -10cmH2O). The firmware program inside the microprocessor 25 uses a state machine architecture and executes the following control logic cyclically at a sampling frequency of 100Hz:

[0052] Step 1 (Pressure Acquisition): The 12-bit ADC module inside the microprocessor 25 continuously samples the analog voltage signal output by the pressure sensor 2 at a sampling rate of 1Msps. The arithmetic mean of 10 samples is taken every 10ms as the current pressure value P. The calculation formula is: P=(V_out-V_offset)×K, where V_out is the voltage value after ADC conversion, V_offset is the zero-point voltage corresponding to atmospheric pressure, and K is the calibration coefficient (unit: cmH2O / V).

[0053] Step 2 (Threshold Comparison): Microprocessor 25 compares the current pressure value P with a preset threshold:

[0054] When P > P_max, the status flag is set to STATE_HIGH;

[0055] When P < P_min, the status flag is set to STATE_LOW;

[0056] When P_min ≤ P ≤ P_max, the status flag is set to STATE_NORMAL.

[0057] Step 3 (Execution Control): The microprocessor 25 performs corresponding actions according to the status flag:

[0058] If it is STATE_HIGH, the timer of the microprocessor 25 outputs a forward pulse sequence. The stepping motor rotates 1 step for each received pulse, the pulse frequency is 1000 Hz, and 20 pulses are continuously output, causing the arc-shaped push plate 27 to move forward by approximately 0.22 mm (20 steps × 0.011 mm / step), and continuously execute until the pressure P drops below P_max;

[0059] If it is STATE_LOW, the microprocessor 25 outputs a reverse pulse sequence, and also outputs 20 reverse pulses, causing the arc-shaped push plate 27 to move backward by approximately 0.22 mm, and continuously execute until the pressure P rises above P_min;

[0060] If it is STATE_NORMAL, the microprocessor 25 stops outputting pulses, and the stepping motor remains in the current position unchanged.

[0061] Step 4 (Watchdog Protection): The independent watchdog (IWDG) timer inside the microprocessor 25 is refreshed at a period of 1 second. If the program runs away or crashes, causing the watchdog not to be refreshed in time, the microprocessor 25 will automatically reset, all output pins will return to the high-impedance state, the stepping motor will stop rotating, and at the same time, the valve handle 13 can be manually operated to ensure that the system can still be used safely in case of abnormalities.

[0062] Through the above program configuration, the microprocessor 25 realizes the full-automatic closed-loop management of real-time acquisition, digital filtering, threshold judgment, and precise control of the pressure signal, forming a complete "perception - decision - execution - feedback" control link, enabling the device to have the intelligent ability to adaptively adjust the drainage speed, effectively reducing the operation burden of medical staff, and at the same time preventing complications caused by sudden changes in body cavity pressure.

[0063] Working Principle: When the device is actually used, first install the control box 23 outside the pinch valve 14, snap the arc-shaped push plate 27 outside the pinch roller 26, and connect the pressure sensor 2, the drive motor 21, and the control box 23 together through the connecting wire 22.

[0064] Medical staff input a pressure safety range (e.g., -5cmH2O to -10cmH2O) through the setting panel 24 according to the patient type (e.g., fetal hydrops, adult pleural effusion, etc.), and this safety range is stored in the microprocessor 25.

[0065] After the device is started, pressure sensor 2 monitors the body cavity pressure or drainage system pressure in real time through the three-way interface 12, and transmits the collected pressure signal to the microprocessor 25 in the control box 23 via the connecting wire 22. The microprocessor 25 compares the real-time received pressure value with the preset pressure safety range on the setting panel 24.

[0066] When the real-time pressure is higher than the preset upper limit (e.g., greater than -5cmH2O, indicating a risk of body cavity compression), the microprocessor 25 sends a control signal to control the drive motor 21 to rotate in the forward direction through the connecting wire 22. The drive motor 21 drives the screw sleeve mechanism to work, causing the arc-shaped push plate 27 to push the clamping roller 26 forward, reducing the degree of compression on the drainage tube 1, thereby increasing the opening of the clamping valve 14 and accelerating the drainage speed.

[0067] When the real-time pressure is lower than the preset lower limit (e.g., less than -10cmH2O, indicating excessive negative pressure and risk of low blood pressure), the microprocessor 25 sends a control signal to control the drive motor 21 to rotate in the opposite direction, causing the arc-shaped push plate 27 to release the clamping roller 26 backward, increasing the degree of compression on the drainage tube 1, thereby reducing the opening of the clamping valve 14 or closing it completely, slowing down or pausing the drainage until the pressure returns to a safe range;

[0068] When the real-time pressure is within the preset safety range, the microprocessor 25 maintains the current control state and keeps the opening of the clamp valve 14 unchanged, so as to achieve uniform and stable drainage.

[0069] Through the aforementioned closed-loop feedback control, the device can automatically adjust the drainage rate according to changes in body cavity pressure, maintaining the pressure within a preset safe range and preventing unstable circulation due to excessively rapid drainage or failure to relieve pressure due to excessively slow drainage. Furthermore, in emergency situations, medical personnel can manually adjust the clamp valve 14 via valve handle 13 for emergency operation.

[0070] The foregoing has only described certain exemplary embodiments of the present invention by way of illustration. Undoubtedly, those skilled in the art can modify the described embodiments in various ways without departing from the spirit and scope of the present invention. Therefore, the foregoing drawings and descriptions are illustrative in nature and should not be construed as limiting the scope of protection of the claims of the present invention.

Claims

1. A pressure-adaptive controlled drainage device for body cavity effusion, characterized in that: Includes a drainage tube (1), the top of which is fixedly connected to a three-way interface (12). A liquid storage bag (11) is connected to the outlet end of the drainage tube (1); A pinch valve (14) is installed on the drainage pipe (1); A pressure sensor (2) is mounted on the three-way interface (12); The drive assembly is connected to the clamp valve (14) in a driving manner; The control box (23) is electrically connected to the pressure sensor (2) and the drive motor (21) respectively. The control box (23) is equipped with a microprocessor (25). And a valve handle (13) is provided on the pinch valve (14).

2. The body cavity effusion pressure adaptive control drainage device according to claim 1, characterized in that: It also includes a setting panel (24), which is located on the control box (23) and electrically connected to the microprocessor (25).

3. The body cavity effusion pressure adaptive control drainage device according to claim 1, characterized in that: The inner side of the clamp valve (14) is provided with a clamp roller (26), and the driving component is a drive motor (21).

4. The body cavity effusion pressure adaptive control drainage device according to claim 3, characterized in that: The output end of the drive motor (21) is fixedly connected to a screw sleeve, and the screw sleeve is internally threaded to a screw rod, and the front end of the screw rod is fixedly connected to an arc-shaped push plate (27), which is connected to the clamping roller (26).

5. The body cavity effusion pressure adaptive control drainage device according to claim 3, characterized in that: The drive motor (21) is a stepper motor.

6. The body cavity effusion pressure adaptive control drainage device according to claim 1, characterized in that: The microprocessor (25) is configured to receive the pressure signal collected by the pressure sensor (2), compare the real-time pressure with the pressure safety range input by the setting panel (24), and control the drive motor (21) to adjust the opening degree of the clamp valve (14) according to the comparison result.

Images