Box body air tightness detection device and box body air tightness detection method

Abstract

The invention relates to a box air tightness detection device and a corresponding box air tightness detection method, which are used for detecting the air tightness of a box body (2801) of a control box of an internal machine of an automatic control system for urinary incontinence, the box body is provided with a bottom, a surrounding side wall and an opening side opposite to the bottom, and a plurality of through parts (2802) are arranged in the side wall. The box airtightness detection device (300) comprises a box clamping tool (310), a liquid pool (320) and a gas input device (330), and the box clamping tool is configured to be used for clamping a box, so that the opening side of the box is hermetically sealed. The liquid tank is configured to receive the cartridge clamping tool (310) together with the cartridge (2801) clamped in the cartridge clamping tool and to completely immerse the cartridge, and wherein the gas supply device is configured to be connected in a gas-tight manner to one of the plurality of perforations when the remaining perforations are closed in a gas-tight manner, and wherein the other perforations are closed in a gas-tight manner. And the gas input part is used for inputting gas into the box body through the through part.

Description

Technical Field

[0001] This disclosure relates to a box airtightness detection device and a box airtightness detection method, used to detect the airtightness of the control box of the internal machine of an automatic urinary incontinence control system. Background Technology

[0002] Urinary incontinence is common among the elderly, and while some treatments exist, many patients lack effective treatment options and rely solely on palliative measures such as continuous catheterization, incontinence pads, or diapers. This leads to a significant decline in their quality of life and causes considerable distress to their families. Therefore, there is a clinical need to develop new devices for treating urinary incontinence.

[0003] Clinically, an artificial urethral sphincter device has been developed. Its advantages include restoring control of urination and allowing urination through the normal urethra without affecting the anatomical structure of the sphincter and surrounding tissues, thus improving the patient's quality of life. However, existing artificial urethral sphincter devices also have some drawbacks. For example, their reliability is relatively low; under certain circumstances, they may exert excessive pressure on the urethral tissue, causing damage.

[0004] An artificial urethral sphincter device may include an external unit and an internal unit. The internal unit can be completely implanted inside the body and performs the main functions of an artificial urethral sphincter. The external unit can be located outside the body and is used to power and communicate with the internal unit, as well as control, display information, and provide alarm functions. The internal unit may include a control box, which houses many important components of the internal unit. The airtightness of the control box is critical. A control box with defective airtightness can pose health risks to the user. Summary of the Invention

[0005] The objective of this application is to provide a box airtightness detection device and a box airtightness detection method for detecting the airtightness of the control box of the internal machine of an automatic urinary incontinence control system, so as to ensure the airtightness of the control box in terms of the box body.

[0006] According to a first aspect of the invention, the task is solved by a box airtightness detection device configured to detect the airtightness of the box body of a control box for an internal machine of an automatic urinary incontinence control system. The box body has a bottom, surrounding side walls, and an open side opposite to the bottom. A plurality of through-holes are provided in the side walls. The box airtightness detection device includes a box body clamping fixture, a liquid pool, and a gas input device. The box body clamping fixture is configured to clamp the box body such that the open side of the box body is airtightly sealed. The liquid pool is configured to contain the box body clamping fixture together with the box body clamped in the box body clamping fixture and to completely immerse the box body. The gas input device is configured to airtightly connect with one of the plurality of through-holes when the other through-holes are airtightly blocked, and to input gas into the box body through the one through-hole.

[0007] With the help of such a box airtightness testing device, the airtightness of the box can be reliably tested, which ensures the airtightness of the control box that is subsequently assembled.

[0008] In some embodiments, the box clamping fixture includes a base with a flat support surface, on which a sealing gasket is placed, and the box can be pressed against the sealing gasket with its open side, so that the open side of the box is airtightly sealed.

[0009] In some embodiments, the box clamping fixture includes a pad for placement on the bottom of the box and a pressing device configured to press the pad toward the box.

[0010] In some embodiments, the pressing device includes a screw, which can press the pad by turning it in one direction and can release the pad by turning it in the opposite direction. Alternatively, an elbow mechanism for pressing the pad is also conceivable.

[0011] In some embodiments, the gas input device is configured as a syringe. Alternatively, an air pump, especially an electric air pump, is also considered.

[0012] According to a second aspect of the invention, the task is solved by a method for detecting the airtightness of a box body for detecting the airtightness of a control box body of an internal machine of an automatic urinary incontinence control system. The box body has a bottom, surrounding side walls, and an open side opposite the bottom. A plurality of through-holes are provided in the side walls. The method for detecting the airtightness of the box body includes the following steps:

[0013] The box body is clamped by a box body clamping fixture, so that the opening side of the box body is airtightly sealed;

[0014] One of the plurality of through-parts is airtightly connected to the gas input device, and the remaining through-parts are airtightly sealed.

[0015] The box-holding fixture, along with the box held within it, is placed in a liquid pool, such that the box is completely submerged below the liquid surface.

[0016] Gas is introduced into the cavity of the box through the gas input device to detect the airtightness of the box. When bubbles from the box appear in the liquid pool, the airtightness of the box is detected as defective, and when no bubbles from the box appear in the liquid pool, the airtightness of the box is detected as intact.

[0017] In some embodiments, the box airtightness testing method can be implemented using a box airtightness testing device according to the first aspect of the present invention. Attached Figure Description

[0018] These and other features, aspects, and advantages of this disclosure will become better understood when the following detailed description is read with reference to the accompanying drawings, in which the same reference numerals denote the same parts, wherein:

[0019] Figure 1 This is a schematic block diagram of an automatic control system for urinary incontinence based on this disclosure;

[0020] Figure 2 This is a circuit block diagram of one embodiment of the external wireless transmission module of the external unit and the internal wireless transmission module of the internal unit of the automatic control system for urinary incontinence according to the present disclosure.

[0021] Figure 3 This is a schematic diagram of the internal mechanism of the automatic control system for urinary incontinence according to this disclosure;

[0022] Figure 4 This is a schematic diagram of the internal structure of the control box of the in vivo machine of the automatic urinary incontinence control system according to the present disclosure;

[0023] Figure 5 This is a schematic diagram of the reservoir of the internal organ of the automatic control system for urinary incontinence according to this disclosure;

[0024] Figure 6 This is a schematic diagram of the first state of the urethral blocker according to this disclosure;

[0025] Figure 7 This is a schematic diagram of the second state of the urethral blocker according to this disclosure;

[0026] Figure 8 This is a schematic diagram of the third state of the urethral blocker according to this disclosure;

[0027] Figure 9 A schematic diagram of a buckle-type urethral blocker in an deployed state according to another embodiment of the present disclosure is shown;

[0028] Figure 10 A schematic diagram of a buckle-type urethral blocker, which is fitted around the urethra and in a fastened state, is shown according to another embodiment of the present disclosure.

[0029] Figure 11 A schematic diagram is shown of a buckle-type urethral blocker clamping the urethra according to another embodiment of the present disclosure;

[0030] Figure 12 A schematic diagram is shown of a buckle-type urethral blocker according to another embodiment of the present disclosure when the urethra is released; and

[0031] Figure 13 This is a schematic diagram of a box airtightness detection device for detecting the airtightness of the control box of an internal machine in an automatic control system for urinary incontinence, according to the present disclosure. Detailed Implementation

[0032] The present disclosure will now be described with reference to the accompanying drawings, which illustrate several embodiments of the present disclosure. However, it should be understood that the present disclosure can be presented in many different ways and is not limited to the embodiments described below; in fact, the embodiments described below are intended to make the disclosure more complete and to fully illustrate the scope of protection of the present disclosure to those skilled in the art. It should also be understood that the embodiments disclosed herein can be combined in various ways to provide further additional embodiments.

[0033] It should be understood that the terminology used in this specification is for describing specific embodiments only and is not intended to limit this disclosure. All terms used in this specification (including technical and scientific terms) have the meanings commonly understood by those skilled in the art, unless otherwise defined. For the sake of brevity and / or clarity, well-known functions or structures may not be described in detail.

[0034] The terms “comprising,” “including,” and “containing” used in the specification indicate the presence of the claimed feature, but do not exclude the presence of one or more other features. The term “and / or” used in the specification includes any and all combinations of one or more of the relevant listed items.

[0035] The use of the terms “connection,” “linked,” or similar terms in the instruction manual is intended to indicate direct and / or indirect connections.

[0036] The system described in this specification can utilize one or more microcontrollers to receive information and transform the received information to generate output. The microcontroller may include any type of computing device, computing circuitry, or any type of microcontroller or processing circuitry capable of executing a series of instructions stored in memory. The microcontroller may include multiple microcontrollers and / or a multi-core central processing unit (CPU) and may include any type of microcontroller. The microcontroller may also include memory to store data and / or algorithms to execute a series of instructions.

[0037] Figure 1 A schematic block diagram of an automatic urinary incontinence control system 1000 according to the present disclosure is shown. The automatic urinary incontinence control system 1000 of the present disclosure is used to treat urinary incontinence caused by sphincter relaxation. The automatic urinary incontinence control system 1000 includes an external unit 100 and an internal unit 200. The internal unit 200 can be completely implanted inside the body and can perform the main functions of an artificial urethral sphincter. The external unit 100 can be located outside the body and can be used to power and communicate with the internal unit, as well as control the internal unit, display information, and provide alarm functions.

[0038] like Figure 1 As shown, the external device 100 may include an external wireless transmission module 110, an external microcontroller 120, and a power module 130. The power module 130 is connected to the external wireless transmission module 110 and the external microcontroller 120, and is used to power the external wireless transmission module 110 and the external microcontroller 120. The power module 130 may be powered by a battery or any other suitable external power source. The external microcontroller 120 is connected to the external wireless transmission module 110. The internal device 200 may include an internal wireless transmission module 210, an internal microcontroller 220, and a urethral blocker 230. The internal microcontroller 220 is connected to the internal wireless transmission module 210. The internal microcontroller 220 is configured to control the urethral blocker 230 to block and release the urethra. The external wireless transmission module 110 is wirelessly coupled to the internal wireless transmission module 210. The external wireless transmission module 110 is configured to transmit electrical energy to the internal wireless transmission module 210 to power the internal device 200. The external wireless transmission module 110 and the internal wireless transmission module 210 can perform bidirectional wireless communication to transmit information.

[0039] Figure 2 A circuit block diagram of one embodiment of the external wireless transmission module 110 and the internal wireless transmission module 210 according to the present disclosure is shown.

[0040] like Figure 2As shown, the external wireless transmission module 110 may include a driving circuit, an external unit information reading / writing circuit, and an external coil Wp1. The internal wireless transmission module 210 may include an internal coil Ws1, an internal unit external information reading circuit, an internal unit internal information writing circuit, and a power supply circuit. The driving circuit is connected to the external coil Wp1 and configured to output an alternating electrical signal to the external coil Wp1. The external coil Wp1 is configured to generate an alternating magnetic field. The internal coil Ws1 is configured to generate an induced electromotive force based on the alternating magnetic field. The power supply circuit is connected to the internal coil Ws1 and provides stable power to the internal unit. The power supply circuit may also be connected to an energy storage element such as a rechargeable battery. The external unit information reading / writing circuit, the internal unit external information reading circuit, and the internal unit internal information writing circuit are configured to modulate the information to be communicated onto electromagnetic waves carrying transmission energy and demodulate the received signal into readable information, thereby bidirectionally transmitting information between the external unit 100 and the internal unit 200. Both the external coil Wp1 and the internal coil Ws1 include magnets, such as low-eddy-current magnets, so that the external coil Wp1 and the internal coil Ws1 can be positioned relative to each other by the new attraction of the magnets, ensuring good coupling between the two coils.

[0041] Therefore, when the external unit 100 supplies power to the internal unit 200, the drive circuit drives a current with a certain waveform through the external coil to generate an alternating magnetic field. This induces an electromotive force in the internal coil Ws1, which is coupled to the external coil. After rectification, filtering, and voltage regulation by the power supply circuit of the internal unit, a stable DC voltage can be provided to other components in the internal unit. When information is transmitted between the external unit 100 and the internal unit 200, the communication information is modulated onto the electromagnetic waves that transmit energy according to certain rules, so that energy and information transmission share a single electromagnetic transmission coil. This achieves the effects of simple structure, high-efficiency energy transmission, and reliable bidirectional information transmission.

[0042] In the external wireless transmission module 110, Wp1 is an external coil used to output energy and information to the internal coil Ws1. The drive circuit outputs an alternating power signal of a certain frequency to the external coil Wp1. The information read / write circuit of the external unit (specifically, the internal information readout circuit of the external unit) includes a current sensing circuit and a comparator. The current sensing circuit is used to detect the current of the external coil Wp1 and convert the current value into a voltage signal. The comparator analyzes the information sent by the internal unit 200 based on the output voltage of the current sensing circuit and the threshold voltage output by the external microcontroller 120. The external microcontroller 120 starts / stops the drive circuit according to a predetermined communication frequency (far lower than the power signal frequency output by the drive circuit) to send information to the internal unit.

[0043] In the in-body wireless transmission module 210, the in-body coil Ws1 receives energy transmitted by the external coil Wp1. The AC signal received by the in-body coil Ws1 is converted into DC voltage through a first matching network and a first rectifier-filter circuit with a first time constant, which is used to provide power to the in-body unit 200. The external information readout circuit of the in-body unit shares the first matching network with the power supply circuit, but uses a second rectifier-filter circuit with a second time constant to convert the presence / absence of energy received by the in-body coil Ws1 into a high / low voltage signal and send it to the in-body microcontroller 220. The first time constant is greater than the second time constant. The signal changing at a predetermined communication frequency can be interpreted as the information transmitted by the external unit, and a low level exceeding a certain duration can be used as a basis for judging the power supply interruption of the external unit 100. The AC switch connects the second matching network to the in-body coil Ws1 according to the information output by the in-body microcontroller 220, causing a change in the equivalent impedance of the corresponding external coil Wp1. In this way, information is transmitted to the external unit 100. In one configuration, the first matching network and the second matching network can be impedance matching networks. The impedance matching network can be a circuit that uses series and parallel reactive elements for impedance matching.

[0044] For the power supply from the external unit 100 to the internal unit 200, an appropriate operating frequency is selected, such as 100kHz to 4MHz, to minimize the overall losses of the transmission coils and switching elements. Both the internal and external coils are impedance matched by connecting appropriate reactive components (capacitors or inductors) in series and / or parallel to improve energy transfer efficiency.

[0045] For wireless information transmission between the external unit 100 and the internal unit 200, to balance requirements for reliable information transmission, electromagnetic compatibility, and energy transmission efficiency, an information transmission baud rate significantly lower than the energy transmission operating frequency is selected. For information transmission from the external unit 100 to the internal unit 200...

[0046] By timely switching the drive of the external coil Wp1 on / off via the drive circuit, the internal unit 200 detects the presence or absence of the output voltage of the internal coil Ws1 and interprets the information according to a predetermined encoding rule. When the internal unit 200 transmits information to the external unit 100, it changes the equivalent impedance of the external coil Wp1 by timely short-circuiting the internal coil Ws1 with an AC switch or an AC switch and a matching capacitor, thereby changing the current of the external coil Wp1. The transmitted information can then be interpreted according to the predetermined encoding rule via a current sensing circuit and a comparator.

[0047] like Figure 1As shown, the external unit 100 may further include a display and control module 140, an alarm module 150, a Bluetooth module 160, and / or a WIFI module. The power module 130 is connected to the display and control module 140, the alarm module 150, the Bluetooth module 160, and / or the WIFI module 170, thereby providing them with power.

[0048] The display and control module 140 is connected to the external microcontroller 120. The display and control module 140 is used to display operating information of the automatic urinary incontinence control system and to input operating commands and parameters. For example, the display and control module 140 can display the remaining battery capacity in real time and prompt for replacement and charging when the capacity reaches a lower limit. The display and control module 140 may include a touchscreen. Alternatively, the display and control module 140 may consist of a separate display screen and an input device such as a keyboard.

[0049] The alarm module 150 is connected to the external microcontroller 120. The alarm module 150 is used to send an alarm signal to the user when the system malfunctions. The alarm signal can be an audible signal and / or a visual signal.

[0050] Bluetooth module 160 and / or WIFI module 170 are connected to the external microcontroller 120. Bluetooth module 160 and / or WIFI module 170 are configured to communicate with a cloud server or a mobile terminal such as a mobile phone, upload system operation status, prompt the patient or caregiver to perform urination operations through the mobile terminal, and monitor the system operation status through APP software on the mobile terminal.

[0051] In use, when the patient inputs a urination command, the external wireless transmission module 110 and the internal wireless transmission module 210 transmit the command to the internal microcontroller 220. The internal microcontroller 220 controls the actuator to release the urethral blocker, initiating urination. When the patient inputs a close command, the wireless communication module transmits the close command to the internal microcontroller 220, which then controls the actuator to close the urethral blocker, ending urination.

[0052] The urethral blocker 230 may include a clamping mechanism. The clamping mechanism can achieve urethral clamping through various driving methods. For example, it can clamp the urethra by inflating or releasing liquid into a bladder fitted over the urethra (hydraulic drive); it can clamp the urethra by using an electromagnet to drive the clamping mechanism based on the principle of electromagnetism (electromagnetic force drive); it can clamp the urethra by using a motor to drive the clamping mechanism (mechanical force generated by the motor); it can clamp the urethra by utilizing the two-way memory effect of a shape memory alloy, such as nickel-titanium alloy, which opens / closes when the temperature changes (force generated by the shape memory alloy when the temperature changes); or it can clamp the urethra by using a bimetallic strip that deforms when the temperature changes due to the difference in the metal's coefficient of thermal expansion (force generated by the bimetallic strip when the temperature changes), and so on.

[0053] In one configuration, at least two urethral obstructions 230 can be placed at different locations in the urethra. Figure 1 and Figure 3 (An example is shown with two urethral occluders). The in vivo microcontroller 220 is configured to control the at least two urethral occluders 230 to alternately block the urethra. That is, during a certain period, one urethral occluder can block the urethra while the other urethral occluders are in a released state; in the next period, the next urethral occluder can block the urethra while the other urethral occluders are in a released state. Each period can be set to 10 minutes, 20 minutes, 30 minutes, or any other reasonable duration, and the in vivo microcontroller 220 controls the urethral occluders to automatically block in turn. In this way, the prolonged clamping of a single location in the urethra can be effectively avoided, preventing tissue blood flow obstruction and tissue necrosis.

[0054] The following example uses hydraulically driven urethral clamping as an illustration, combined with... Figures 3 to 8 It provides a detailed description of the internal organs and the structure of the urethral blocker within them.

[0055] like Figure 3 and Figure 4As shown, in addition to the structures described above, the in vivo machine 200 also includes a pump 240 (e.g., a micro pump), a solenoid valve 250 (e.g., a micro solenoid valve), a circuit board 260 with the in vivo microcontroller 220 described above, and a reservoir 270. The flow rate of the pump 240 can be 3 mL / min-40 mL / min. The pressure of the pump 240 can be 5-120 kPa. The pump 240, the solenoid valve 250, and the circuit board 260 are housed within a control box 280. The pump 240 and the solenoid valve 250 are connected to the in vivo microcontroller 220 on the circuit board 260 for control by the in vivo microcontroller 220. The reservoir 270, the urethral blocker 230, and the in vivo coil Ws1 described above are disposed outside the control box 280. The reservoir 270, the urethral blocker 230, and the reservoir 270 are connected to the pump 240 and the solenoid valve 250 within the control box 280 via corresponding connecting pipes 290. The connecting tube can be made of silicone or any other suitable material.

[0056] The control box 280 includes a box body 2801 and a box cover. To demonstrate the components of the internal unit 200 housed within the control box 280, Figure 4 The cover of the control box 280 has been removed. The box body 2801 has multiple through-holes 2802 in one of its side walls for guiding conduits and cables. In the current embodiment, there are two through-holes 2802 for liquid conduits and one through-hole 2802 for cables.

[0057] Figure 5 A schematic structure of the reservoir 270 is shown. The reservoir 270 can be made of silicone rubber material that meets the requirements of implantation biocompatibility. The reservoir 270 can be oblate-spherical in shape to store and deliver the fluid required for the urethral blocker. The reservoir 270 can be equipped with a refill injection valve 2701 for percutaneous injection of refill fluid. The refill injection valve 2701 can be integrally formed with the reservoir 270 or connected to the reservoir 270 as a separate component via a conduit. The refill injection valve 2701 can be button-shaped. The puncture surface of the refill injection valve 2701 is elastic, for example, it can be a high-density rubber membrane. This allows the puncture surface to recover due to its own elasticity after the needle is withdrawn after refilling, thus maintaining the seal of the reservoir 270. A needle-blocking plate 2702 can be provided on the opposite side of the puncture surface. The needle-blocking plate 2702 may be made of a puncture-resistant material to prevent the reservoir 270 from being punctured during fluid replenishment. The material may be, for example, PET plastic, a metal plate, or the like. The reservoir 270 has inlet and outlet ports, which are connected to the outside via a connecting tube 290.

[0058] Figures 6 to 8An embodiment of a urethral occluder 230 is shown. As shown, the urethral occluder 230 includes a C-shaped sac 2301. The C-shaped sac 2301 surrounds the urethra 10 below the bladder neck. The C-shaped sac 2301 forms an open annular sac. The open annular sac allows for smooth insertion of catheters or similar devices into the urethra in patients with tissue edema, avoiding urethral injury. The C-shaped sac can be made of silicone or any other suitable material. When the urethral occluder is inflated with fluid (e.g., saline), the C-shaped sac inflates and pressurizes, and the inner side of the C-shaped sac bulges to compress the urethra and close it (e.g., Figure 6 (As shown); when the fluid inside the urethral occluder is released, the C-shaped balloon relaxes, the urethra opens, and urination is completed (as shown). Figure 7 (As shown). The C-shaped sac 2301 is connected to the reservoir 270 via a connecting tube 290, a pump 240, and a solenoid valve 250 to receive liquid from the reservoir 270 and release liquid into the reservoir 270. The in vivo microcontroller 220 controls the filling and emptying of the C-shaped sac 2301 by controlling the pump 240 and the solenoid valve 250.

[0059] In one configuration, the urethral blocker 230 further includes a support ring 2302 located outside the C-shaped balloon 2301. The support ring 2302 can be configured to elastically deform and open when the pressure within the support ring 2302 exceeds a threshold (e.g., ...). Figure 8 As shown), when the pressure within the support ring 2302 returns to below the threshold value, it reverts to its original shape before elastic deformation (as shown). Figure 6 and Figure 7 (As shown). The support ring 2302 can also be configured to maintain its shape when the pressure within the support ring 2302 is less than or equal to the threshold. In one configuration, the support ring 2302 is configured to maintain a constant elastic force during elastic deformation. The threshold can be set to 20 kPa, or for female patients, the threshold can be set to 15 kPa, and for male patients, the threshold can be set to 20 kPa. The threshold can also be set to other reasonable pressure values.

[0060] The support ring 2302 can be made of a material with a superelastic effect, such as a nickel-titanium alloy or other similar materials. The support ring 2302 can also be made of at least two spring sheets. The support ring 2302 and the C-shaped bladder 2301 can be molded together using a mold with silicone rubber die casting.

[0061] By employing the support ring 2302 as described above, when the pressure of the contents (including tissue, C-shaped cysts, etc.) within the support ring exceeds a threshold due to tissue edema or other reasons, such as Figure 8As shown, the support ring expands gradually due to elastic deformation, providing a buffer space for tissues such as the urethra and preventing tissue ischemia and necrosis and upper urinary tract lesions caused by uncontrollable prolonged urethral obstruction or excessive bladder pressure. When the pressure decreases, the support ring automatically returns to its original position and resumes its function.

[0062] In one configuration, the support ring 2302 is designed with the shape as described below. For example... Figure 6 As shown, the support ring may include a first segment 2302A, a second segment 2302B, a third segment 2302C, and a fourth segment 2302D connected in sequence. The second segment 2302B and the third segment 2302C constitute the C-shaped main body of the support ring 2302. The first segment 2302A bends from one end of the second segment 2302B in a direction opposite to the bending direction of the second segment 2302B, and the fourth segment 2302D bends from one end of the third segment 2302C in a direction opposite to the bending direction of the third segment 2302C. Figure 6 As shown, the first segment 2302A and the fourth segment 2302D first approach each other from one end of the second segment 2302B and the third segment 2302C, respectively, until they contact each other and then move away from each other. The shape of the support ring 2302 as described above allows it to provide constant force support for the urethral blocker under normal conditions, while allowing tissue to smoothly escape from the opening formed by the first segment 2302A and the fourth segment 2302D in the event of excessive internal pressure.

[0063] In one configuration, a pressure sensor 2303 is disposed between the C-shaped bladder 2301 and the support ring 2302. The support ring 2302, the C-shaped bladder 2301, and the pressure sensor 2303 can be molded together using a silicone rubber die-casting mold. The pressure sensor 2303 is, for example, a thin-film pressure sensor or any suitable pressure sensor. The pressure sensor 2303 is connected to the in vivo microcontroller 220 to send the sensed pressure signal to the in vivo microcontroller 220. The in vivo microcontroller 220 can acquire the pressure detection value detected by the pressure sensor 2303 in real time (e.g., every 100 ms).

[0064] When the pressure detection value exceeds the maximum pressure setting value, the in vivo microcontroller 220 controls the pump and solenoid valve to release the corresponding urethral blocker 230 to release the urethra. This improves system safety, thereby ensuring patient safety. Preferably, when the pressure detection value exceeds the maximum pressure setting value, the in vivo microcontroller 220 sends an alarm signal to the external unit 100, causing the alarm module 150 of the external unit 100 to sound an alarm, and the in vivo microcontroller 220 releases the corresponding urethral blocker 230 after a set delay (e.g., 10 seconds), thus giving the patient sufficient preparation time and improving the user experience.

[0065] When the pressure detection value in the urethral occluder 230, which is in a fluid-filled state, is lower than the minimum pressure setting value, the in vivo microcontroller 220 controls the pump and solenoid valve to fill the C-shaped sac 2301 of the urethral occluder 230 with fluid until the pressure of the C-shaped sac 2301 meets the requirements. In this way, through pressure feedback and automatic pressure adjustment, the system can operate normally even with a small amount of leakage. The maximum and minimum pressure settings mentioned above can be personalized according to the patient's individual circumstances.

[0066] In addition, the system also employs multiple safety protection measures to ensure that all urethral blockers will be released when the system malfunctions or power fails, allowing the urethra to remain free. This ensures that the system will not cause prolonged urethral closure and lead to upper urinary tract lesions when it fails, thus improving the safety and reliability of the system.

[0067] In one configuration, the in vivo microcontroller 220 is configured to detect the power supply voltage of the in vivo device 200 in real time (e.g., every 100 ms). For example, the in vivo microcontroller 220 can determine whether the power supply voltage of the in vivo device is normal by detecting the potential signal in the external information readout circuit of the in vivo device. The in vivo microcontroller 220 is configured to control the pump and solenoid valve to immediately stop the filling of the urethral blocker when an abnormal power supply voltage of the in vivo device is detected, and then continue to detect the power supply voltage of the in vivo device in real time; if the power supply voltage is still abnormal after a set period of time (e.g., 30 s), the in vivo microcontroller 220 controls the pump and solenoid valve to release the entire urethral blocker to loosen the urethra; if the power supply voltage returns to normal after a set period of time (e.g., 30 s), the in vivo microcontroller 220 resumes normal control of the pump and solenoid valve.

[0068] The following reference Figures 9-12 This description describes a urethral blocker 230 according to another embodiment of the present disclosure, which is configured as a buckle-type urethral blocker. Figures 9-12Only one exemplary urethral blocker 230 of the in vivo machine 200 is shown in the description above, while other aspects of the in vivo machine 200 can be referred to in the description above. It is understood that the in vivo machine 200 may have one or two such urethral blockers 230 for alternately clamping and releasing the urethra 10.

[0069] like Figure 9 As shown, the urethral blocker 230 according to this disclosure includes a connecting tube 290, a fluid-filled bladder 2312, a snap-fit ​​structure, and a flexible band 2315.

[0070] The inflatable bladder 2312 can be made of silicone or any other suitable material. In use, the inflatable bladder 2312 surrounds the patient's urethra 10 and is pressurized by the injection of liquid. When the inflatable bladder is pressurized, it clamps the patient's urethra 10, thereby closing the urethra; when the liquid in the inflatable bladder is expelled and the pressurization is released, the inflatable bladder relaxes the patient's urethra 10, thereby opening the urethra and allowing urine to drain from the urethra 10.

[0071] The connecting tube 290 is used to inject liquid into the filling sac 2312 (not shown) via the reservoir 270 and to receive liquid discharged from the filling sac 2312. One end of the connecting tube is connected to the filling sac 2312. Optionally, the connecting tube 290 can be connected to the filling sac via the collection section 2318. The other end (not shown) of the connecting tube 290 can be detachably connected to a device for supplying liquid to the buttonhole urethral blocker, such as a pump.

[0072] The snap-fit ​​structure includes a first snap-fit ​​portion and a second snap-fit ​​portion. The first snap-fit ​​portion can engage with the second snap-fit ​​portion. The first snap-fit ​​portion can be a snap-fit ​​protrusion 2313. The second snap-fit ​​portion can be a snap-fit ​​hole 2314. The first snap-fit ​​portion and the second snap-fit ​​portion can also be any other structure capable of engaging with each other. When the first snap-fit ​​portion and the second snap-fit ​​portion are engaged with each other, the snap-fit ​​urethral blocker can be held in the engaged state around the urethra 10, such as... Figure 10 As shown.

[0073] In the urethral blocker 230 of this disclosure, which is in the form of a buckle-type urethral blocker, the connecting tube 290 and the optional collection portion 2318 are separately provided from the snap-fit ​​structure (i.e., the first snap-fit ​​portion and the second snap-fit ​​portion). In one configuration, the snap-fit ​​structure can be provided on the flexible band 2315. The snap-fit ​​protrusion 2313 and the snap-fit ​​hole 2314 can be respectively provided at both ends of the flexible band 2315. The connecting tube 290 and the optional collection portion 2318 can be provided between the snap-fit ​​protrusion 2313 and the snap-fit ​​hole 2314. With this arrangement, when the buckle-type urethral blocker is wrapped around the urethra 10, it is not necessary to pass the connecting tube 290 through the snap-fit ​​hole 2314 of the snap-fit ​​structure; instead, it is only necessary to pass the separately provided snap-fit ​​protrusion 2313 through the snap-fit ​​hole 2314 and fasten the two together. Thus, during the installation of the buckle-type urethral occluder of this disclosure, the other end (not shown) of the connecting tube 290 of the buckle-type urethral occluder can always be connected to other auxiliary devices (e.g., a pump for supplying fluid). Therefore, before the buckle-type urethral occluder of this disclosure is installed around the urethra 10, for example during the manufacture of the buckle-type urethral occluder of this disclosure, fluid can be filled into the filling bladder of the buckle-type urethral occluder, and during the installation process, the fluid passage of the buckle-type urethral occluder of this disclosure can always remain isolated from the outside environment, thereby reducing the complexity of the operation during surgery and improving the success rate of the surgery by preventing blood from entering the fluid passage.

[0074] The flexible band 2315 is formed of a material suitable for implantation in the human body. Specifically, the flexible band 2315 can be made of a flexible material with a certain degree of elasticity. The flexible material can, for example, be formed of a combination of silicone and polymer materials. With this type of flexible material, the operator can easily wrap the buckle-type urethral blocker around the patient's urethra 10.

[0075] When the first snap fastener is not engaged with the second snap fastener, the buckle-type urethral blocker is in the deployed state. Figure 9 As shown, in the unfolded state, the flexible band 2315 can be formed as a plane. A fluid-filled bladder 2312 can be disposed on one side of the flexible band 2315. In one configuration, the fluid-filled bladder 2312 extends along a portion of the length of the flexible band 2315, allowing the operator's hand to easily grasp the flexible band for operation. A connecting tube 290 and an optional collection portion 2318 can be disposed on the flexible band 2315. In one configuration, the connecting tube 290 and the optional collection portion 2318 can be disposed on the opposite side of the flexible band 2315 from the side where the fluid-filled bladder is disposed. Thus, when the buckle-type urethral blocker is wrapped around the urethra 10, as... Figure 10As shown, the inflatable balloon 2312 can be positioned on the side in contact with the urethra 10, while the snap-fit ​​protrusion 2313 and connecting tube 290 are positioned on the side facing the operator, thus facilitating operation. During installation, the operator can position the side of the inflatable balloon 2312 towards the patient's urethra 10, wrap the flexible band 2315 around the patient's urethra 10, then pass the snap-fit ​​protrusion 2313 through the snap-fit ​​hole 2314 and fasten the two together, thereby obtaining the desired result. Figure 10 The buckle-type urethral blocker shown is fitted around the urethra 10 and in a fastened state. It is evident that the buckle-type urethral blocker of this disclosure is simple and convenient to install, and during installation, there is no need to disconnect the other end (not shown) of the connecting tube 290 from other additional devices.

[0076] In one configuration, the latching protrusion 2313 may be provided with a traction portion 2316 for easy gripping by the operator. The traction portion 2316 may be a traction post extending from the latching protrusion 2313 or any structure that facilitates gripping by the operator. During the engagement operation of the latching protrusion 2313 and the latching hole 2314, the operator can grip the traction portion, allowing the latching protrusion 2313 to easily pass through the latching hole 2314, which greatly facilitates the operator's operation.

[0077] The traction portion 2316 is configured to be removable. For example, the traction portion 2316 may be bonded, welded, or otherwise attached to the snap-fit ​​protrusion 2313. After the snap-fit ​​urethral blocker has been held in the engaged position around the urethra, the traction portion 2316 may be cut off.

[0078] During the manufacturing process, the flexible strip 2315, the liquid filling bladder 2312, the snap-fit ​​protrusion 2313, the connecting tube 290, and the optional liquid collection part 2318 can be molded into one piece by a molding process.

[0079] The working process of the buckle-type urethral occlusion device disclosed herein is as follows: Figure 11 and Figure 12 As shown. After the buckle-type urethral occlusion device is held in the buckled state around the urethra 10, if it is necessary to block the urethra 10, liquid can be further injected into the filling balloon 2312 through the connecting tube 290 to increase the pressure in the filling balloon 2312. In this case, as Figure 11 As shown, the inflatable bladder applies pressure to the urethra 10 to clamp it, thereby blocking the flow of urine in the urethra 10; if it is necessary to release the blockage of the urethra, the fluid in the inflatable bladder 2312 can be allowed to flow out through the connecting tube 290 from the inflatable bladder 2312 to a reservoir bladder 270 (not shown) to reduce the pressure in the inflatable bladder 2312, in which case, as Figure 12 As shown, the inflatable bladder relieves the pressure on the urethra, thus relaxing the urethra and allowing urine to flow through it.

[0080] Now, referring to Figure 13 To illustrate, the housing airtightness detection device 300 according to this disclosure is configured to detect the airtightness of the housing 2801 of the control housing 280 of the internal machine 200 of the urinary incontinence automatic control system 1000. Here, the airtightness of the control housing 280 of the internal machine 200 is critical, and therefore, the airtightness of the housing 2801 itself is critical. Therefore, the airtightness of the housing 2801 can be detected by means of the housing airtightness detection device 300 before assembling the internal machine 200.

[0081] like Figure 13 As shown, the box airtightness testing device 300 includes a box clamping fixture 310 and a liquid pool 320 schematically indicated by dashed lines. The box clamping fixture 310 includes a base 301 with a flat support surface, on which a sealing gasket 302 can be placed. The box 2801 is placed on the sealing gasket 302 with its open side, that is, the side of the box 2801 facing the lid, or the side of the box 2801 that is sealed to the lid. Figure 13 A pad 304 can be placed on the bottom of the upper part of the box, and a pressing device 303 above the pad 304 can press the pad 304 against the box body 2801. Here, the pressing device 303 may include a screw, wherein the screw can press the pad 304 by turning it in one direction, and can release the pad 304 by turning it in the opposite direction.

[0082] One of the through-holes 2802 of the housing 2801 can be connected to the gas input device 330 via a conduit 305, while the other through-holes 2802 can be blocked, for example, with a rubber stopper. Here, the gas input device 330 is configured as a syringe. Alternatively, an air pump is also considered. By pushing the syringe, gas, especially air, can be introduced into the cavity of the housing 2801.

[0083] Here, the box body 2801 is generally rectangular in shape, including a bottom and an open side opposite the bottom, and a surrounding peripheral wall with a rectangular outline. Each through-hole 2802 may be provided only in one side wall of the entire peripheral wall. Alternatively, the box body 2801 may also be cylindrical or elliptical, including a bottom and an open side opposite the bottom, and a surrounding peripheral wall that is circular or elliptical.

[0084] The box clamping fixture 310, along with the box 2801 installed therein, can be submerged in a liquid pool. For example, the liquid pool can be a cuboid or cylindrical container, open at the top to allow the box clamping fixture 310, along with the box 2801, to be placed into the container from the top. The liquid in the liquid pool can be, for example, purified water or saline solution. Gas can be introduced into the cavity of the box 2801 via the gas input device 330. When the box 2801 is properly sealed, no gas will escape from the box 2801 into the liquid pool, and therefore no bubbles will be observed coming from the box 2801. Conversely, if the box 2801 is poorly sealed, gas will escape from the box 2801 into the liquid pool, and bubbles will be observed coming from the box 2801. It is understandable that the size and volume of the liquid pool should be designed to ensure that the box 2801 is completely submerged below the liquid surface.

[0085] By using the box airtightness testing device 300 to test the airtightness of the box 2801 itself in advance, waste can be reduced during the manufacturing process of the internal machine 200, ensuring the high quality of the internal machine 200.

[0086] Although only specific embodiments of this disclosure are illustrated and described herein, various modifications and variations will be apparent to those skilled in the art. Therefore, it should be understood that the appended claims are intended to cover all modifications and variations falling within the true spirit and scope of this disclosure.

Claims

1. A box-type airtightness detection device, comprising a box (2801) for detecting the airtightness of a control box (280) of an internal machine (200) of an automatic incontinence control system (1000), the box having a bottom, surrounding side walls, and an opening side opposite the bottom, wherein a plurality of through portions (2802) are provided in the side walls, characterized in that, The box airtightness testing device (300) includes a box clamping fixture (310), a liquid pool (320), and a gas input device (330). The box clamping fixture is configured to clamp the box so that the opening side of the box is airtightly sealed. The liquid pool is configured to contain the box clamping fixture (310) together with the box (2801) clamped in the box clamping fixture and to completely immerse the box. The gas input device is configured to airtightly connect with one of the plurality of through-holes when the other through-holes are airtightly blocked, and to input gas into the box through the one through-hole.

2. The box airtightness testing device according to claim 1, characterized in that, The box clamping fixture (310) includes a base (301) with a flat support surface, on which a sealing gasket (302) is placed, and the box (2801) can press its open side against the sealing gasket so that the open side of the box is airtightly sealed.

3. The box airtightness testing device according to claim 1 or 2, characterized in that, The box clamping fixture (310) includes a pad (304) for placement on the bottom of the box (2801) and a pressing device (303) configured to press the pad toward the box.

4. The box airtightness testing device according to claim 3, characterized in that, The extrusion device (303) includes a screw, which can extrude a pad (304) by being screwed in one direction and can release the pad by being screwed in the opposite direction.

5. The box airtightness testing device according to claim 1 or 2, characterized in that, The gas input device (330) is configured as a syringe.

6. A method for detecting the airtightness of a housing, used to detect the airtightness of the housing (2801) of the control box (280) of the internal machine (200) of an automatic incontinence control system (1000), said housing having a bottom, surrounding side walls, and an opening side opposite to the bottom, wherein a plurality of through portions (2802) are provided in said side walls, characterized in that, The method for testing the airtightness of the housing includes the following steps: The box body is clamped by the box body clamping fixture (310) so that the opening side of the box body is airtightly sealed; One of the plurality of through-parts is airtightly connected to the gas input device (330), and the remaining through-parts are airtightly sealed. The box-holding fixture (310), together with the box (2801) held in the fixture, is placed in the liquid pool (320), such that the box is completely submerged below the liquid surface of the pool; and Gas is introduced into the cavity of the box through the gas input device (330) to detect the airtightness of the box. When bubbles from the box appear in the liquid pool, the airtightness of the box is detected as defective, and when no bubbles from the box appear in the liquid pool, the airtightness of the box is detected as intact.

7. The method for detecting the airtightness of a box according to claim 6, characterized in that, The box airtightness testing method is implemented using the box airtightness testing device according to any one of claims 1 to 5.

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