Urinary incontinence automatic control system and internal machine

Abstract

The invention relates to an automatic control system for urinary incontinence and an internal machine thereof. The in-vivo machine comprises a liquid storage bag, a pump, a urethra blocker, a main electromagnetic valve and a urethra blocker electromagnetic valve, the pump is in fluid connection with the liquid storage bag and the urethra blocker, the urethra blocker electromagnetic valve is arranged between the pump and the urethra blocker, the main electromagnetic valve is in fluid connection with the liquid storage bag and the urethra blocker, and the main electromagnetic valve is in fluid connection with the liquid storage bag and the urethra blocker. A pressure sensor is disposed between the pump and the urethral blocker. The in-vivo machine comprises an in-vivo microcontroller, and the in-vivo microcontroller is configured to respond to a signal used for clamping and closing the urethra, turn off a main electromagnetic valve, turn on a urethra blocker electromagnetic valve and start a pump until the liquid pressure detected by a pressure sensor exceeds a preset pressure threshold value, and then stop working of the pump and turn off the urethra blocker electromagnetic valve for pressure maintaining; and in response to a signal for loosening the urethra, opening a solenoid valve in a flow path from the urethral interrupter to the reservoir.

Description

Technical Field

[0001] This disclosure relates to an automatic control system for urinary incontinence and an internal organ for the automatic control system for urinary incontinence. 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. Summary of the Invention

[0004] The objective of this application is to provide an automatic control system for urinary incontinence and an internal device for the automatic control system for urinary incontinence, thereby enabling reliable clamping and loosening of the urethra.

[0005] According to a first aspect of the invention, the task is solved by an in vivo device for controlling urinary incontinence, the in vivo device being configured for complete implantation within the body, characterized in that the in vivo device includes a reservoir, a pump, a urethral blocker, a master solenoid valve, and a urethral blocker solenoid valve; the pump is fluidly connected to the reservoir on one side and to the urethral blocker on the other side; the urethral blocker solenoid valve is disposed between the pump and the urethral blocker; the master solenoid valve is fluidly connected to the reservoir on one side and to the urethral blocker on the other side; and a pressure sensor is disposed between the pump and the urethral blocker; and

[0006] The in vivo device includes an in vivo microcontroller configured to control a urethral occluder to block and release the urethra, wherein the in vivo microcontroller is configured to...

[0007] - In response to a signal for clamping the urethra, the main solenoid valve is closed, the urethral occluder solenoid valve is closed, and the pump is started, allowing fluid to be delivered from the reservoir to the urethral occluder until the fluid pressure detected by the pressure sensor exceeds a predetermined pressure threshold. Immediately afterwards, the pump stops operating, and the urethral occluder solenoid valve is closed to maintain pressure.

[0008] - In response to a signal for releasing the urethra, a solenoid valve in the flow path from the urethral blocker to the reservoir is activated, causing the fluid in the urethral blocker to return to the reservoir.

[0009] In some embodiments, the main solenoid valve is fluidly connected to the reservoir on one hand and connected between the urethral blocker solenoid valve and the urethral blocker on the other hand.

[0010] In some embodiments, the main solenoid valve is fluidly connected to the reservoir on one hand and connected between the pump and the urethral blocker solenoid valve on the other hand.

[0011] In some embodiments, the pressure sensor is positioned between the urethral blocker solenoid valve and the urethral blocker.

[0012] In some embodiments, the pressure sensor is positioned between the pump and the urethral blocker solenoid valve.

[0013] In some embodiments, the in vivo device includes two parallel urethral occluders positioned at different locations in the urethra, each urethral occluder equipped with a urethral occluder solenoid valve, a pump fluidly connected on one side to a reservoir and on the other side to the parallel structure of the two urethral occluders, the urethral occluder solenoid valves being disposed between the pump and the respective urethral occluders, a master solenoid valve fluidly connected on one side to the reservoir and on the other side to the parallel structure of the two urethral occluders, and an in vivo microcontroller configured to control the two urethral occluders to alternately block and release the urethra.

[0014] In some embodiments, a respective pressure sensor is provided between each urethral blocker and its associated urethral blocker solenoid valve.

[0015] In some embodiments, a common pressure sensor for the two urethral blockers is provided between the pump and the parallel structure of the two urethral blockers.

[0016] In some embodiments, the in vivo microcontroller is configured to cyclically perform the following steps at predetermined time intervals in order to control the two urethral occluders to alternately block and release the urethra:

[0017] - First, load one of the two urethral occluders, the one that has been unloaded. To do this, close the main solenoid valve, open the solenoid valve of the urethral occluder associated with the unloaded urethral occluder, close the other solenoid valve, and start the pump to deliver fluid from the reservoir to the urethral occluder until the fluid pressure delivered to the urethral occluder, as detected by the pressure sensor, exceeds a predetermined pressure threshold. Then, immediately stop the pump and close the solenoid valve of the urethral occluder to maintain pressure.

[0018] - Connect the main solenoid valve and the other urethral blocker solenoid valve to allow the fluid in the loaded other urethral blocker to return to the reservoir.

[0019] In some embodiments, the urethral blocker includes a clamping mechanism that achieves clamping by hydraulic pressure, electromagnetic force, mechanical force generated by a motor, force generated by a shape memory alloy when the temperature changes, or force generated by a bimetallic strip when the temperature changes.

[0020] In some embodiments, the urethral blocker includes a C-shaped sac that can be filled and drained with fluid.

[0021] In some embodiments, the in vivo machine further includes a control box in which the pump, the solenoid valve, and the in vivo microcontroller are housed.

[0022] In some embodiments, the urethral blocker further includes a support ring located outside the C-shaped sac, the support ring being configured to elastically deform and open when the pressure within the support ring exceeds a threshold.

[0023] In some embodiments, the support ring is configured to maintain its shape or return to its original shape before elastic deformation when the pressure within the support ring is less than or equal to the threshold.

[0024] In some embodiments, the support ring is configured to maintain a constant elastic force during elastic deformation.

[0025] In some embodiments, the support ring is made of a material with a superelastic effect or is made of a combination of at least two spring plates, wherein the material is preferably a nickel-titanium alloy.

[0026] In some embodiments, the support ring includes a first segment, a second segment, a third segment, and a fourth segment connected in sequence, wherein the second segment and the third segment constitute a C-shaped main body portion of the support ring, the first segment bends from one end of the second segment in a direction opposite to the bending direction of the second segment, and the fourth segment bends from one end of the third segment in a direction opposite to the bending direction of the third segment, wherein the first segment and the fourth segment first approach each other from one end of the second segment and one end of the third segment respectively until they contact each other and then move away from each other.

[0027] In some embodiments, the reservoir is provided with a refill injection valve having a resilient puncture surface.

[0028] In some embodiments, a needle-blocking plate is provided on the opposite side of the puncture surface.

[0029] In some embodiments, the in vivo microcontroller is configured to control the pump and solenoid valve to release the entire urethral blocker to loosen the urethra if an abnormal supply voltage is detected and remains abnormal after a given time.

[0030] In some embodiments, the in vivo microcontroller is configured to control the pump and solenoid valve to immediately stop the filling of the urethral blocker when an abnormal power supply voltage is detected.

[0031] In some embodiments, the in vivo microcontroller is configured to resume normal control of the at least one pump and solenoid valve upon detecting an abnormal supply voltage and the supply voltage returning to normal after a given time.

[0032] In some embodiments, the in vivo device also includes a protection circuit independent of the in vivo microcontroller, which is triggered when a signal received by the in vivo device from the outside is at a low potential for more than a set time, thereby controlling the pump and solenoid valve to release all urethral obstruction and loosen the urethra.

[0033] In some implementations, the power supply circuitry of the internal organ includes an energy storage element.

[0034] In some implementations, each solenoid valve has a storage capacitor.

[0035] In some embodiments, an additional pressure sensor is provided between the C-shaped bladder and the support ring.

[0036] In some embodiments, the in vivo microcontroller is connected to the additional pressure sensor to acquire pressure values ​​detected by the additional pressure sensor in real time. When the pressure value exceeds a corresponding maximum pressure setting, the in vivo microcontroller controls the pump and solenoid valve to release the corresponding urethral blocker to loosen the urethra.

[0037] In some embodiments, the in vivo microcontroller is connected to the additional pressure sensor to acquire the pressure value detected by the additional pressure sensor in real time. When the pressure detection value in the urethral blocker in the fluid-filled state is less than the minimum pressure setting value, the in vivo microcontroller controls the pump and solenoid valve to fill the C-shaped sac of the urethral blocker with fluid.

[0038] In some embodiments, the flow rate of the pump 240 is 3 mL / min to 40 mL / min, and the pressure of the pump is 5 to 120 kPa.

[0039] In some embodiments, the in vivo device further includes an in vivo wireless transmission module, the in vivo microcontroller is connected to the in vivo wireless transmission module, and the in vivo wireless transmission module is configured to wirelessly obtain power from outside the body and to perform bidirectional wireless communication with outside the body.

[0040] In some embodiments, the urethral occluder is a buckle-type urethral occluder, which includes a connecting tube, a fluid-filled bladder, and a snap-fit ​​structure. The connecting tube is connected to the fluid-filled bladder and is used to inject liquid into the bladder and receive liquid discharged from the bladder. 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 so that the buckle-type urethral occluder is held in a snapped state around the urethra. The connecting tube is separate from the first snap-fit ​​portion and the second snap-fit ​​portion.

[0041] In some embodiments, the first latching part is a latching protrusion, and the second latching part is a latching hole.

[0042] In some embodiments, the buckle-type urethral blocker further includes a flexible band, with the buckle protrusion and the buckle hole located at both ends of the flexible band, and the connecting tube located between the buckle protrusion and the buckle hole.

[0043] In some embodiments, the fluid-filled bladder is disposed on one side of the flexible strip, and the snap-fit ​​protrusion and the connecting tube are disposed on the opposite side of the flexible strip.

[0044] In some embodiments, the flexible strip unfolds into a plane when the buckle protrusion is not engaged with the buckle hole.

[0045] In some embodiments, the buckle-type urethral blocker is configured to be pre-filled with liquid before being installed around the urethra.

[0046] In some embodiments, the buckle protrusion is provided with a traction part that facilitates the operator's grip.

[0047] In some embodiments, the traction portion is configured to be removable.

[0048] According to a second aspect of the invention, the task is solved by an automatic urinary incontinence control system comprising an external unit located outside the body and an internal unit according to a first aspect of the invention.

[0049] In some embodiments, the external device includes an external wireless transmission module, an external microcontroller, and a power module. The power module is configured to supply power to the external wireless transmission module and the external microcontroller. The external microcontroller is connected to the external wireless transmission module. The external wireless transmission module is wirelessly coupled to the internal wireless transmission module. The external wireless transmission module is configured to transmit electrical energy to the internal wireless transmission module, and the external wireless transmission module and the internal wireless transmission module are capable of bidirectional wireless communication.

[0050] In some embodiments, the external device further includes a display and control module connected to the external microcontroller for displaying operating information of the urinary incontinence automatic control system and inputting operation commands and parameters.

[0051] In some implementations, the display and control module includes a touchscreen.

[0052] In some embodiments, the external device further includes an alarm module connected to the external microcontroller for sending alarm signals of system malfunction to the user.

[0053] In some embodiments, the external device further includes a Bluetooth module and / or a WIFI module, which are configured to communicate with a cloud server or a mobile terminal. Attached Figure Description

[0054] 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:

[0055] Figure 1 This is a schematic block diagram of an automatic control system for urinary incontinence based on this disclosure;

[0056] Figure 2This 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.

[0057] Figure 3 This is a schematic diagram of the internal mechanism of the automatic control system for urinary incontinence according to this disclosure;

[0058] 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;

[0059] 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;

[0060] Figure 6 This is a schematic diagram of the first state of the urethral blocker according to this disclosure;

[0061] Figure 7 This is a schematic diagram of the second state of the urethral blocker according to this disclosure;

[0062] Figure 8 This is a schematic diagram of the third state of the urethral blocker according to this disclosure;

[0063] 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;

[0064] 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.

[0065] Figure 11 A schematic diagram is shown of a buckle-type urethral blocker clamping the urethra according to another embodiment of the present disclosure;

[0066] 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;

[0067] Figure 13 This is a schematic diagram of a fluid circuit connection of the internal machine of the automatic control system for urinary incontinence according to the present disclosure;

[0068] Figure 14 yes Figure 13 A schematic diagram of the first flow state of the fluid circuit connection shown;

[0069] Figure 15 yes Figure 13 A schematic diagram of the second flow state of the fluid circuit connection shown;

[0070] Figure 16yes Figure 13 A schematic diagram of the third flow state of the fluid circuit connection shown;

[0071] Figure 17 yes Figure 13 A schematic diagram of the fourth flow state of the fluid circuit connection shown;

[0072] Figure 18 yes Figure 13 A schematic diagram of the fifth flow state of the fluid circuit connection shown; and

[0073] Figure 19 This is a schematic diagram of the fluid circuit connection of the internal organ according to another embodiment of the automatic control system for urinary incontinence of this disclosure.

[0074] Figure 20 This is a schematic diagram of the fluid circuit connection of the internal organ according to another embodiment of the automatic control system for urinary incontinence of this disclosure. Detailed Implementation

[0075] 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.

[0076] 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.

[0077] 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.

[0078] The use of the terms “connection,” “linked,” or similar terms in the instruction manual is intended to indicate direct and / or indirect connections.

[0079] 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.

[0080] 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.

[0081] 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.

[0082] 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.

[0083] 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 alternating electrical signals 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 signals 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.

[0084] 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.

[0085] 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 detects the current of the external coil Wp1 and converts 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.

[0086] 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.

[0087] 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.

[0088] 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...

[0089] 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.

[0090] 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.

[0091] 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.

[0092] 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.

[0093] 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.

[0094] 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.

[0095] 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.

[0096] 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.

[0097] 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.

[0098] 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.

[0099] 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 control box 280 has been removed. Box 2801 has multiple through-holes in one of its side walls for guiding conduits and cables. In the current embodiment, there are two through-holes for liquid conduits and one through-hole for cables.

[0100] 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.

[0101] 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.

[0102] 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.

[0103] 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.

[0104] 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 the urethra and other tissues. This prevents tissue ischemia and necrosis, as well as 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.

[0105] 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.

[0106] 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).

[0107] When the pressure detection value exceeds the maximum pressure setting value, the in vivo microcontroller 220 controls the pump 240 and the solenoid valve to release the corresponding urethral blocker 230 to release the urethra. This improves system safety and ensures 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 delays for a set time (e.g., 10 seconds) before releasing the corresponding urethral blocker 230, thus giving the patient sufficient preparation time and improving the user experience.

[0108] 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.

[0109] 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.

[0110] In one configuration, the in vivo microcontroller 220 is configured to detect the power supply voltage of the in vivo device 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.

[0111] 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.

[0112] 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.

[0113] 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.

[0114] 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.

[0115] 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.

[0116] 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.

[0117] 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.

[0118] 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.

[0119] 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.

[0120] 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.

[0121] 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.

[0122] 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.

[0123] As described above, the internal organ 200 can be equipped with at least two urethral obstructors 230 at different locations in the urethra. In this case, each urethral obstructor 230 can have the following characteristics: Figures 6 to 8 Or such as Figures 9 to 12 And the structure described above. Figures 13 to 18 The fluid circuit connection of the in vivo machine 200 is illustrated by way of example in an embodiment with two urethral obstructions 230 (denoted by reference numerals 230a and 230b for ease of description). However, those skilled in the art will appreciate that more than two urethral obstructions can be provided, in which case it is only necessary to... Figure 13 A new urethral blocker is connected in parallel at point O of the fluid path shown, and a new solenoid valve is connected in series with the new urethral blocker.

[0124] like Figure 13 As shown, the internal organ 200 includes a reservoir 270, a pump 240, a first urethral blocker 230a, a second urethral blocker 230b, and multiple solenoid valves 250. These solenoid valves 250 include a master solenoid valve 250A, a first urethral blocker solenoid valve 250a, and a second urethral blocker solenoid valve 250b. The first ends of the first urethral blocker solenoid valve 250a and the second urethral blocker solenoid valve 250b are respectively connected to the first urethral blocker 230a and the second urethral blocker 230b. The second ends of the first urethral blocker solenoid valve 250a and the second urethral blocker solenoid valve 250b are each connected to the first end of the main solenoid valve 250A. The second end of the main solenoid valve 250A is connected to the inlet and outlet of the reservoir 270. The first end of the pump 240 is connected to the second ends of the first urethral blocker solenoid valve 250a and the second urethral blocker solenoid valve 250b. The second end of the pump 240 is connected to the inlet and outlet of the reservoir 270.

[0125] As in Figure 13 Indicated by solid lines, each urethral blocker can be equipped with its own pressure sensor 200P to detect the liquid pressure in the pipeline between the corresponding solenoid valves 250a, 250b and the corresponding urethral blockers 230a, 230b.

[0126] Alternatively, it is also possible, such as in Figure 13 As indicated by dashed lines, each urethral blocker 230a and 230b may be equipped with a common pressure sensor 200P for detecting the liquid pressure in the pipeline between the pump 240 and the parallel structure of each urethral blocker 230a and 230b.

[0127] For the sake of simplicity, the pressure sensor 200P mentioned above is only mentioned in... Figure 13The illustration is in the middle, while Figures 14 to 18 The following is omitted:

[0128] Figure 14 and Figure 15 The diagram schematically illustrates the principle of the first urethral blocker 230a clamping the urethra while the second urethral blocker 230b releasing the urethra. As shown, firstly, the internal microcontroller 220 controls the pump 240 to start, opening the first urethral blocker solenoid valve 250a (i.e., connecting the corresponding pipeline), while the main solenoid valve 250A and the second urethral blocker solenoid valve 250b close (i.e., shutting off the corresponding pipeline). At this time, the liquid in the reservoir 270 is injected into the first urethral blocker 230a through the pump 240 and the first urethral blocker solenoid valve 250a. The liquid in the first urethral blocker 230a continuously increases and expands, completely closing the urethra. When the pressure detected by the pressure sensor 200P, which is located between the first urethral blocker solenoid valve 250a and the first urethral blocker 230a as mentioned above, or by the common pressure sensor 200P mentioned above, exceeds a predetermined pressure threshold, the in vivo microcontroller 220 sends a control signal based on the pressure signal from the pressure sensor 200P, causing the pump 240 to stop working, the first urethral blocker solenoid valve 250a to close and maintain pressure, and at the same time, the main solenoid valve 250A and the second urethral blocker solenoid valve 250b to open, the liquid in the second urethral blocker 230b to return to the reservoir 270 through its own tension, and the second urethral blocker 230b to release, loosening the clamp on the urethra.

[0129] Figure 16 and Figure 17The diagram schematically illustrates the principle of the second urethral blocker 230b clamping the urethra while the first urethral blocker 230a releases it. As shown, firstly, the internal microcontroller 220 controls the pump 240 to start, opening the second urethral blocker solenoid valve 250b, while closing the main solenoid valve 250A and the first urethral blocker solenoid valve 250a. At this time, liquid in the reservoir 270 is injected into the second urethral blocker 230b through the pump 240 and the second urethral blocker solenoid valve 250b. The liquid in the second urethral blocker 230b continuously increases and expands, completely closing the urethra. When the pressure detected by the pressure sensor 200P, which is located between the second urethral blocker solenoid valve 250b and the second urethral blocker 230b as mentioned above, or by the common pressure sensor 200P mentioned above, exceeds a predetermined pressure threshold, the in vivo microcontroller 220 sends a control signal based on the pressure signal from the pressure sensor 200P, causing the pump 240 to stop working, the second urethral blocker solenoid valve 250b to close and maintain pressure, and at the same time, the main solenoid valve 250A and the first urethral blocker solenoid valve 250a to open, the liquid in the first urethral blocker 230a to return to the reservoir 270 through its own tension, and the first urethral blocker 230a to release, loosening the clamp on the urethra.

[0130] Figure 18 The diagram schematically illustrates the flow state with all urethral blockers fully released. When urination is required, the main solenoid valve 250A, the first urethral blocker solenoid valve 250a, and the second urethral blocker solenoid valve 250b are all opened. The fluid in the first urethral blocker 230a and the second urethral blocker 230b flows back into the reservoir 270 through each solenoid valve due to its own tension and the internal urethral pressure from the bladder. Each urethral blocker releases the pressure on the urethra, and urine is then expelled from the body through the urethra.

[0131] In this way, it can be ensured that the two urethral occluders automatically take turns compressing the urethra at regular intervals (e.g., every 20 minutes), preventing tissue necrosis caused by prolonged clamping of the urethra and obstruction of blood flow.

[0132] Figure 19 This is a schematic diagram of the fluid circuit connection of the internal unit 200 according to another embodiment of the urinary incontinence automatic control system 1000 of this disclosure. In this embodiment, the internal unit 200 includes only a single urethral blocker 230. Here, as in Figure 19 The pressure sensor 200P, indicated by the solid line, can be positioned between the urethral blocker solenoid valve 250a and the urethral blocker 230; alternatively, such as in Figure 19The pressure sensor 200P, indicated by the dashed line, can also be positioned between the pump 240 and the urethral blocker solenoid valve 250a. When urethral closure is required, the internal microcontroller 220 controls the main solenoid valve 250A to close (i.e., shut off the corresponding tubing), and the urethral blocker solenoid valve 250a to open (i.e., connect the corresponding tubing), and controls the pump 240 to start. At this time, the liquid in the reservoir 270 is injected into the urethral blocker 230 through the pump 240 and the urethral blocker solenoid valve 250a. The liquid in the urethral blocker 230 continuously increases and expands, completely closing the urethra. When the liquid pressure detected by the pressure sensor 200P exceeds a predetermined pressure threshold, the internal microcontroller 220 sends a control signal based on the pressure signal from the pressure sensor 200P, causing the pump 240 to stop working and the urethral blocker solenoid valve 250a to close and maintain pressure. When it is necessary to release the urethra, the internal microcontroller 220 controls the opening of both the main solenoid valve 250A and the urethral blocker solenoid valve 250a. As a result, the fluid in the urethral blocker 230 returns to the reservoir 270 by its own tension, and the urethral blocker 230 is released, releasing the clamp on the urethra.

[0133] Figure 20 This is a schematic diagram of the fluid circuit connection of the internal organ 200 according to another embodiment of the urinary incontinence automatic control system 1000 of this disclosure. Figure 20 The implementation method and the method Figure 15 The difference in the implementation method is that: in accordance with Figure 19 In one embodiment, the side of the main solenoid valve 250A opposite to the reservoir 270 is connected between the pump 240 and the urethral blocker solenoid valve 250a; while in the press Figure 20 In one embodiment, the side of the main solenoid valve 250A away from the reservoir 270 is connected between the urethral blocker solenoid valve 250a and the urethral blocker 230.

[0134] In this embodiment, the internal organ 200 also includes only a single urethral blocker 230. Here, as in... Figure 20 The pressure sensor 200P, indicated by the solid line, can be positioned between the urethral blocker solenoid valve 250a and the urethral blocker 230; alternatively, such as in Figure 20 The pressure sensor 200P, indicated by the dashed line, can also be installed between the pump 240 and the urethral blocker solenoid valve 250a.

[0135] When urethral closure is required, the internal microcontroller 220 controls the system to close the main solenoid valve 250A (i.e., shut off the corresponding tubing), open the urethral blocker solenoid valve 250a (i.e., connect the corresponding tubing), and start the pump 240. At this time, liquid in the reservoir 270 is injected into the urethral blocker 230 via the pump 240 and the urethral blocker solenoid valve 250a. The liquid in the urethral blocker 230 continuously increases and expands, completely closing the urethra. When the liquid pressure detected by the pressure sensor 200P exceeds a predetermined pressure threshold, the internal microcontroller 220 sends a control signal based on the pressure signal from the pressure sensor 200P, causing the pump 240 to stop working and the urethral blocker solenoid valve 250a to close and maintain pressure. When urethral release is required, the internal microcontroller 220 controls the system to open the main solenoid valve 250A. Therefore, the liquid in the urethral blocker 230 returns to the reservoir 270 through its own tension, releasing the urethral blocker 230 and loosening the urethral closure. Optionally, the urethral blocker solenoid valve 250a can also be opened at this time.

[0136] 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. An in vivo machine for controlling urinary incontinence, said in vivo machine being configured for complete implantation in the body, characterized in that, The internal device includes a reservoir (270), a pump (240), a urethral blocker (230, 230a, 230b), a main solenoid valve (250A), and urethral blocker solenoid valves (250a, 250b). The pump is fluidly connected to the reservoir on one side and to the urethral blocker on the other. The urethral blocker solenoid valves are located between the pump and the urethral blocker. The main solenoid valve is fluidly connected to the reservoir on one side and to the urethral blocker on the other. A pressure sensor (200P) is located between the pump and the urethral blocker. The in vivo device includes an in vivo microcontroller (220) configured to control a urethral occluder to block and release the urethra, wherein the in vivo microcontroller is configured to... - In response to a signal for clamping the urethra, the main solenoid valve is closed, the urethral occluder solenoid valve is closed, and the pump is started, allowing fluid to be delivered from the reservoir to the urethral occluder until the fluid pressure detected by the pressure sensor exceeds a predetermined pressure threshold. Immediately afterwards, the pump stops operating, and the urethral occluder solenoid valve is closed to maintain pressure. - In response to a signal for releasing the urethra, a solenoid valve in the flow path from the urethral blocker to the reservoir is activated, causing the fluid in the urethral blocker to return to the reservoir.

2. The in-vivo machine of claim 1, wherein, The main solenoid valve (250A) is fluidly connected to the reservoir (270) on one side and connected between the urethral blocker solenoid valve and the urethral blocker on the other side.

3. The in-vivo machine of claim 1, wherein, The main solenoid valve (250A) is fluidly connected to the reservoir (270) on one side and connected between the pump and the urethral blocker solenoid valve on the other side.

4. The in vivo mechanism according to any one of claims 1 to 3, characterized in that, The pressure sensor (200P) is located between the urethral blocker solenoid valve and the urethral blocker.

5. The in vivo mechanism according to any one of claims 1 to 3, characterized in that, The pressure sensor (200P) is located between the pump and the solenoid valve of the urethral blocker.

6. The in vivo mechanism according to any one of claims 1 to 3, characterized in that, The in vivo machine (200) includes two parallel urethral blockers (230a, 230b) for placement at different locations in the urethra, each urethral blocker being equipped with a urethral blocker solenoid valve (250a, 250b). The pump (240) is fluidly connected to a reservoir (270) on one side and to the parallel structure of the two urethral blockers on the other side. The urethral blocker solenoid valve is disposed between the pump and the corresponding urethral blocker. The main solenoid valve (250A) is fluidly connected to the reservoir on one side and to the parallel structure of the two urethral blockers on the other side. The in vivo microcontroller (220) is configured to control the two urethral blockers to alternately block and release the urethra.

7. The in vivo mechanism according to claim 6, characterized in that, Each pressure sensor is provided between each urethral blocker and its associated urethral blocker solenoid valve.

8. The in vivo mechanism according to claim 6, characterized in that, A common pressure sensor for the two urethral blockers is provided between the pump and the parallel structure of the two urethral blockers.

9. The in vivo mechanism according to claim 6, characterized in that, The in vivo microcontroller is configured to cyclically execute the following steps at predetermined time intervals in order to control the two urethral occluders to alternately block and release the urethra: - First, load one of the two urethral occluders, the one that has been unloaded. To do this, close the main solenoid valve, open the solenoid valve of the urethral occluder associated with the unloaded urethral occluder, close the other solenoid valve, and start the pump to deliver fluid from the reservoir to the urethral occluder until the fluid pressure delivered to the urethral occluder, as detected by the pressure sensor, exceeds a predetermined pressure threshold. Then, immediately stop the pump and close the solenoid valve of the urethral occluder to maintain pressure. - Connect the main solenoid valve and the other urethral blocker solenoid valve to allow the fluid in the loaded other urethral blocker to return to the reservoir.

10. An automatic control system for urinary incontinence, said automatic control system for urinary incontinence (1000) comprising an external unit (100) located outside the body, characterized in that, The automatic control system for urinary incontinence further includes an in vivo machine (200) according to any one of claims 1 to 9.

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