An umbilical cord prolapse reduction and perfusion maintenance integrated device

Abstract

The present application relates to a kind of umbilical cord prolapse reduction and perfusion maintenance integrated device, belong to medical instrument technical field, including split and close self-locking base, ball joint connecting seat, catheter tail connector, fine diameter multi-cavity catheter, elastic lifting capsule, integrated micro-doppler probe and color scale ring belt.The first exposed part of fetus is lifted away from internal orifice of cervix by elastic lifting capsule to relieve umbilical cord compression, and the internal pressure in lifting is kept stable under transport jolt by pressure feedback closed loop adaptive regulation filling medium pumping, the perfusion state can be confirmed in real time during transport by integrated micro-doppler probe, the catheter route is universally adjusted and friction self-locking by ball joint connecting seat, and the lifting height is directly indicated without power supply by color scale ring belt.The device fundamentally changes the traditional mode of manual continuous lifting for umbilical cord prolapse first aid, realizes the self-maintenance of instrument umbilical cord perfusion, and significantly improves the safety and convenience of operation of first aid transport.

Description

Technical Field

[0001] This invention belongs to the field of medical device technology and relates to an integrated device for umbilical cord prolapse reduction and perfusion maintenance. Background Technology

[0002] In obstetric emergencies, umbilical cord prolapse is a high-risk factor for perinatal mortality. After the amniotic sac ruptures, the umbilical cord prolapses through the external cervical os, compressing the presenting part of the fetus between the fetal part and the maternal pelvis, interrupting umbilical cord blood flow and causing irreversible and severe hypoxic injury to the fetus within a short period. Currently, clinical emergency treatment relies entirely on manual umbilical cord reduction, where the operator inserts their hand into the birth canal and continuously pushes upwards the presenting part of the fetus to relieve umbilical cord compression, maintaining this position throughout transport and preoperative preparation. This procedure is highly dependent on manual labor; bumps during transport and the operator's physical exertion can easily cause hand displacement, leading to renewed compression of the umbilical cord. Furthermore, the operator's hand and forearm occupy space around the vaginal opening, interfering with preoperative aseptic sterilization. In addition, after reduction, relying solely on fetal heart rate monitoring to indirectly determine whether umbilical cord blood flow has been restored has a significant physiological time lag, making it impossible to confirm the perfusion status in real time.

[0003] Various instruments for reducing umbilical cord prolapse have emerged in the current technology. Although they employ different structures such as pouch compression, folding struts, reduction gloves, and sheath isolation, they all share the common feature of being designed for handheld operation. The proximal end of the instrument is a handle or directly worn on the hand, requiring the operator to hold it continuously to maintain the instrument's position within the uterine cavity; releasing the grip means the instrument becomes ineffective. This design is essentially still an "extension of the hand inside the body," failing to overcome the predicament of "operator being locked by the instrument." In the delivery room environment requiring rapid transfer, handheld instruments not only fail to solve the problem of passive fluctuations in pushing force due to bumps, but also severely interfere with preoperative preparation and teamwork because they occupy the operator's hands.

[0004] Therefore, a long-standing technological gap exists in the field of existing umbilical cord prolapse emergency devices: on the one hand, even with devices that utilize fluid-filled bladders for decompression, the internal pressure during transport passively changes due to bumps and the gravitational fluctuations of the presenting part, lacking the ability to adaptively adjust the pumping of filling media based on pressure feedback. This results in unstable lifting height and difficulty in maintaining continuous umbilical cord perfusion under dynamic conditions. On the other hand, post-insertion assessment relies heavily on indirect judgment using fetal heart rate monitoring, lacking real-time objective feedback on the umbilical artery perfusion status. Furthermore, existing devices generally lack an integrated system where the operator can release their hands after insertion, and the device itself can be securely fixed to the transport bed via an external anchoring structure while continuously maintaining umbilical cord perfusion. How to fundamentally transform the device from a hand-held dependent to an externally self-anchored, unattended mode, and embed objective perfusion monitoring and adaptive pressure maintenance functions, has become a key clinical requirement for improving the safety and operational efficiency of umbilical cord prolapse emergency care. Summary of the Invention

[0005] In view of this, the purpose of this invention is to propose an integrated device for umbilical cord prolapse reduction and perfusion maintenance to solve the following technical problems in the prior art: (1) Most umbilical cord prolapse emergency devices are handheld structures, and the operator cannot release their hands to participate in other emergency operations after the reduction is completed. Moreover, the device lacks a self-fixing structure independent of the operator during the transport process and cannot stably maintain the lifting position in the body; (2) There are existing devices that use fluid bladders to decompress, but the lifting internal pressure changes passively under the transport bumps and gravity fluctuations of the presenting part of the fetus. They lack the ability to adaptively adjust the pumping of filling medium based on pressure feedback, making it difficult to maintain umbilical cord perfusion under dynamic conditions; (3) After reduction, there is a lack of real-time objective auditory feedback on the recovery status of fetal umbilical artery perfusion, and there is a physiological time lag due to reliance on fetal heart monitoring.

[0006] To achieve the above objectives, the present invention provides the following technical solution:

[0007] An integrated device for umbilical cord prolapse reduction and perfusion maintenance includes a detachable self-locking base. A fixed clamping arm is fixedly mounted at the lower end of the detachable self-locking base. A movable clamping arm is hinged to the fixed clamping arm via an integrated pin. A quick-clamping handle is connected to the tail end of the movable clamping arm via a flip shaft. A ball-joint connector is bolted to the upper end of the detachable self-locking base. A ball head is embedded in the inner cavity of the ball-joint connector. A quick-release slot is fixedly mounted on the top of the ball head. A catheter tail connector is detachably connected to the quick-release slot. A small-diameter multi-lumen catheter extends rearward and is fixedly connected to the small-diameter multi-lumen catheter. An elastic lifting capsule is heat-sealed to the outer periphery of the front end of the small-diameter multi-lumen catheter. An integrated micro-Doppler probe is embedded in the upper surface of the elastic lifting capsule. A control display box is fixedly mounted on the side of the detachable self-locking base. The control and display box contains a microcontroller. This box is connected via circuitry to the integrated micro-Doppler probe, a pressure sensor located within the fluid-filled passage of the elastic support bladder, and a micro-pump that pumps warm, sterile saline solution into the elastic support bladder through the inflation port. The elastic support bladder is inflated with warm, sterile saline solution through the inflation fluid channel, non-impactily lifting the presenting part of the fetus away from the internal cervical os to relieve umbilical cord compression. The microcontroller adaptively adjusts the output of the micro-pump based on the real-time feedback of the bladder's internal pressure from the pressure sensor, maintaining stable internal pressure and lifting height even under transport bumps and fluctuations in the presenting part's gravity. The integrated micro-Doppler probe acquires the umbilical artery blood flow frequency shift signal in real time, which is demodulated into audio output by the microcontroller to confirm the umbilical cord perfusion status.

[0008] Furthermore, the ball joint connector includes a hemispherical seat and a damping washer embedded in the cavity of the hemispherical seat, with the ball head embedded in the cavity of the damping washer.

[0009] Furthermore, the quick-release slot is a T-shaped quick-release slot, which consists of an upper inlet section and a lower locking section. The locking section is provided with an elastic locking pin, which is composed of a miniature compression spring and a tapered pin. The side of the conduit tail connector is integrally provided with a quick-release block, the outer profile of which matches the inner profile of the T-shaped quick-release slot. When the quick-release block is pushed into the bottom of the locking section, the tapered pin automatically springs into the corresponding locking hole. The slot is unlocked when the release button of the elastic locking pin is pressed.

[0010] Furthermore, the side of the catheter tail connector is provided with an inflation port and a Doppler signal output port. The inflation port is a Luer connector, and the Doppler signal output port is a coaxial connector.

[0011] Furthermore, the cross-section of the narrow-diameter multi-lumen catheter is provided with three independent parallel channels: a main working channel, an inflation fluid channel, and a signal line channel. The main working channel runs through the entire length of the narrow-diameter multi-lumen catheter and its front end opens at the distal end face of the narrow-diameter multi-lumen catheter. The front end of the inflation fluid channel is connected to the inner cavity of the elastic support bladder and its tail end is led out through the inflation interface. The signal line channel is used to pass through the shielded signal line of the integrated micro Doppler probe.

[0012] Furthermore, the upper surface of the elastic support bag is a shallow concave arc surface, the lower surface of the elastic support bag is a flat surface, the upper surface of the elastic support bag is provided with multiple radial drainage grooves, and the edge of the elastic support bag is provided with two symmetrical umbilical cord protection notches.

[0013] Furthermore, the integrated micro Doppler probe is embedded at the geometric center of the shallow concave arc surface on the upper surface of the elastic support capsule, and the outer periphery of the integrated micro Doppler probe is sealed and fixed by a silicone sealing ring. The acoustic window of the integrated micro Doppler probe faces upwards from the upper surface of the elastic support capsule.

[0014] Furthermore, the outer wall of the thin-diameter multi-lumen catheter is provided with a colored graduated ring from the root of the elastic support capsule backward, and the colored graduated ring is provided with a color segment every five millimeters.

[0015] Furthermore, the front end of the thin-diameter multi-lumen catheter is provided with an integrally injection-molded hemispherical silicone buffer head, and the outer wall of the thin-diameter multi-lumen catheter is provided with a corrugated anti-slip section composed of multiple annular convex lines at a set distance from the front end.

[0016] Furthermore, the control and display box integrates a microcontroller, a rechargeable lithium battery, a Bluetooth module, a display screen, an audio amplifier module, and a micro speaker. The microcontroller receives the frequency shift signal from the integrated micro Doppler probe and outputs it to the audio amplifier module to drive the micro speaker to play the umbilical artery blood flow audio signal in real time. The microcontroller also adaptively controls the start, stop, and speed of the micro air pump based on the deviation between the pressure inside the bladder fed back by the pressure sensor in real time and the set target lifting pressure, using a closed-loop adjustment algorithm, so that the lifting pressure inside the elastic lifting bladder dynamically converges to the target lifting pressure.

[0017] The microcontroller is embedded with a real-time blood flow audio demodulation algorithm and a closed-loop adjustment algorithm. The real-time blood flow audio demodulation algorithm uses a sliding window of length N to capture the frequency shift signal of the integrated micro Doppler probe. After weighting the discrete signal sequence within the window using the Hanning window function, a fast Fourier transform is performed to obtain the blood flow velocity power spectrum, and the frequency corresponding to the peak value of the power spectrum amplitude is taken as the instantaneous blood flow frequency shift peak value. The closed-loop adjustment algorithm adjusts the output of the micro air pump in conjunction with the instantaneous blood flow frequency shift peak value and the intracystic pressure fed back by the pressure sensor to maintain the stability of the umbilical artery perfusion index.

[0018] The beneficial effects of this invention are as follows:

[0019] This invention integrates a bed rail self-anchoring structure, a universal self-locking posture maintenance structure, and a non-stuffing elastic lifting structure into a single device for umbilical cord prolapse reduction and irrigation maintenance. The device is securely clamped to the side rail of the transport bed via a detachable self-locking base, allowing the operator to immediately free their hands to participate in other emergency procedures after umbilical cord repositioning. The elastic lifting sac, with its controllable expansion height at the tip of a thin-diameter multi-lumen catheter, gently lifts the presenting part away from the internal cervical os without occupying the main volume of the uterine cavity, greatly ensuring the safety of intrauterine procedures during labor and avoiding damage to the uterine wall. The constant tension device outputs real-time audio signals of umbilical artery blood flow through a miniature Doppler probe integrated on the surface of the capsule, allowing medical staff to instantly confirm the umbilical cord perfusion status by hearing during transport, avoiding judgment delays caused by delayed fetal heart rate monitoring. The ball-joint connector enables universal adjustment of the catheter route and friction self-locking, ensuring a stable lifting position under transport bumps. A color-coded graduated ring provides intuitive indication of the lifting height without the need for power, significantly improving the mechanization sustainability and transport safety of umbilical cord prolapse emergency care, and reducing the physical burden and manpower required for operators.

[0020] This invention organically combines three elements: a non-packing lifting system filled with warm, sterile saline solution, closed-loop adaptive pressure maintenance based on pressure sensor feedback, and real-time audio confirmation of umbilical artery perfusion using an integrated micro Doppler probe. All three are coordinated by a microcontroller within a control and display box, decoupling decompression and perfusion maintenance under dynamic conditions to achieve a stable balance. This allows for the continuous and stable maintenance of the umbilical artery perfusion index while relieving umbilical cord compression, significantly improving the safety of emergency transport and extending umbilical cord tolerance time.

[0021] Other advantages, objectives, and features of the invention will be set forth in part in the description which follows, and in part will be apparent to those skilled in the art from the following examination, or may be learned from practice of the invention. The objectives and other advantages of the invention can be realized and obtained through the following description. Attached Figure Description

[0022] To make the objectives, technical solutions, and advantages of the present invention clearer, the preferred embodiments of the present invention will be described in detail below with reference to the accompanying drawings, wherein:

[0023] Figure 1 This is a front view of the overall structure of the present invention;

[0024] Figure 2 This is a side view of the main structure of the present invention;

[0025] Figure 3 This is a rear view of the main structure of the present invention;

[0026] Figure 4 This is a top view of the main structure of the present invention (sectional view).

[0027] Figure 5 This is a sectional view of the ball joint connector.

[0028] Figure 6 This is a logic block diagram of the system control relationships;

[0029] Figure 7 This is a block diagram showing the connection and signal transmission relationship of the device.

[0030] Reference numerals: 1. Separable self-locking base; 2. Fixed clamping arm; 3. Integrated pin; 4. Movable clamping arm; 5. Flip shaft; 6. Quick clamping handle; 9. Ball joint connector; 10. Hemispherical seat; 11. Damping washer; 12. Ball head; 13. Quick-release slot seat; 14. Catheter tail connector; 15. Inflation interface; 16. Doppler signal output interface; 17. Small-diameter multi-lumen catheter; 18. Elastic lifting bladder; 19. Integrated miniature Doppler probe; 21. Main working channel; 22. Inflation fluid channel; 23. Signal line channel; 25. Hemispherical silicone buffer head; 26. Corrugated anti-slip section; 27. Radial drainage groove; 28. Umbilical cord protection notch; 29. ​​Silicone sealing ring. Detailed Implementation

[0031] The following specific examples illustrate the implementation of the present invention. Those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification. The present invention can also be implemented or applied through other different specific embodiments, and various details in this specification can be modified or changed based on different viewpoints and applications without departing from the spirit of the present invention. It should be noted that the illustrations provided in the following embodiments are only schematic representations of the basic concept of the present invention. Unless otherwise specified, the following embodiments and features can be combined with each other.

[0032] The accompanying drawings are for illustrative purposes only and are schematic diagrams, not actual pictures. They should not be construed as limiting the invention. To better illustrate the embodiments of the invention, some parts in the drawings may be omitted, enlarged, or reduced, and do not represent the actual product dimensions. It is understandable to those skilled in the art that some well-known structures and their descriptions may be omitted in the drawings.

[0033] In the accompanying drawings of the embodiments of the present invention, the same or similar reference numerals correspond to the same or similar components. In the description of the present invention, it should be understood that if terms such as "upper," "lower," "left," "right," "front," and "rear" indicate the orientation or positional relationship based on the orientation or positional relationship shown in the drawings, they are only for the convenience of describing the present invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, the terms used to describe positional relationships in the drawings are only for illustrative purposes and should not be construed as limiting the present invention. For those skilled in the art, the specific meaning of the above terms can be understood according to the specific circumstances.

[0034] like Figure 1-7As shown, one embodiment of the present invention provides an integrated device for umbilical cord prolapse reduction and perfusion maintenance. The overall structure is composed of two main parts: an anchoring module and an insertion module, which are combined by a detachable and detachable connection structure. The anchoring module is responsible for firmly clamping the entire device to the side rail of the medical transport bed and realizing universal adjustment and self-locking maintenance of the catheter entry direction. The insertion module is responsible for entering the uterine cavity through the vagina and cervical canal to lift the presenting part of the fetus upward to relieve the pressure on the prolapsed umbilical cord and provide real-time feedback on the umbilical cord blood flow perfusion status.

[0035] The core of the anchoring module is the detachable self-locking base 1. The detachable self-locking base 1 is made entirely of medical-grade stainless steel sheet, stamped and passivated. This material possesses corrosion resistance suitable for long-term use in environments with repeated immersion and wiping in chlorine-containing disinfectant solutions. An integrally extended fixing arm 2 is fixedly installed at the lower end of the detachable self-locking base 1. The fixing arm 2 has a C-shaped arc profile, and its inner surface is fixed with an arc-shaped anti-slip rubber pad using medical-grade silicone adhesive. The arc-shaped anti-slip rubber pad is made of elastic silicone with moderate Shore hardness. When clamping and closing, it can fully conform to the outer contour of bed rails with different cross-sectional shapes through its own elastic deformation, while providing a large static friction force to prevent slippage along the rail after clamping. The middle of the fixing arm 2 is hinged to the movable arm 4 via an integral pin 3. Anti-removal springs are provided at both ends of the integral pin 3 to ensure that the movable arm 4 will not accidentally loosen during use. The movable arm 4 can swing freely within a certain angle range around the integral pin 3 to open and close the clamping opening. The tail end of the movable clamping arm 4 is rotatably connected to a quick-clamping handle 6 via a flipping shaft 5. The front face of the quick-clamping handle 6 is machined with an involute cam surface. When the quick-clamping handle 6 flips upward, this cam surface presses against the end face of the fixed clamping arm 2, driving the movable clamping arm 4 to swing and close around the integrated pin 3 towards the fixed clamping arm 2. When the quick-clamping handle 6 flips downward, the pressing relationship between the cam surface and the end face of the fixed clamping arm 2 is released, and the movable clamping arm 4 automatically opens under the elastic restoring force of its own material, achieving rapid release. The clamping opening formed by the fixed clamping arm 2 and the movable clamping arm 4 in the closed state is adapted to the outer contour of the circular or rectangular tube of the standard medical transport bed side rail. An arc-shaped anti-slip rubber pad deforms within this clamping opening with the closing force, filling the microscopic gap between the metal rail surface and the clamping arm, thereby establishing a stable frictional locking mechanism.

[0036] The upper end of the detachable self-locking base 1 is fixedly connected to a ball joint connector 9 by three bolts. The ball joint connector 9 includes a hemispherical seat 10, which is precision cast from aluminum alloy and then anodized to form a dense, corrosion-resistant surface layer. The inner cavity of the hemispherical seat 10 is a precision-machined hemispherical concave surface, in which a damping washer 11 is embedded. The damping washer 11 is made of medical-grade high-elasticity silicone, which does not undergo permanent compression deformation under long-term pressure and remains chemically stable in repeated contact with disinfectant. A ball head 12 is tightly embedded in the inner cavity of the damping washer 11. The ball head 12 is also precision cast from aluminum alloy and its surface is precision ground to a smooth mirror finish. The ball head 12 can rotate omnidirectionally in any direction within the inner cavity of the damping washer 11, and its rotation range is mechanically constrained by the opening edge of the hemispherical seat 10 within a conical surface with a apex angle of approximately 90 degrees. The damping washer 11 applies a uniform radial elastic compressive force to the surface of the ball head 12. This compressive force is converted into a static friction torque in any posture after the ball head 12 stops rotating, allowing the ball head 12 to remain self-locked in this posture without the need for an additional locking knob or braking mechanism. A connecting post extends integrally from the top of the ball head 12, and a quick-release slot seat 13 is fixedly installed at the top of the connecting post. The quick-release slot seat 13 has a T-shaped quick-release slot, which is formed by a wider upper inlet section and a narrower lower locking section, creating an inverted T-shaped sliding cavity. An elastic locking pin is installed inside the locking section of the T-shaped quick-release slot. The elastic locking pin consists of a miniature compression spring and a tapered pin. One end of the miniature compression spring abuts against a spring seat on the inner wall of the locking section, while the other end pushes the tapered pin so that it partially extends into the sliding cavity space of the locking section in a free state, forming a passive automatic locking mechanism against the corresponding locking hole on the side of the inserted part. When the release button of the elastic latch is pressed, the tapered pin overcomes the thrust of the miniature compression spring and exits the latch hole to unlock.

[0037] The detachable connection between the insertion module and the anchoring module is achieved by the catheter tail connector 14 in conjunction with the quick-release slot seat 13. The catheter tail connector 14 is injection molded from medical-grade polyetheretherketone (PEEK) material, which has excellent biocompatibility and mechanical strength, maintaining dimensional stability under repeated insertion and removal and axial force conditions. A quick-release block extends integrally from the side of the catheter tail connector 14. The outer cross-sectional shape of the quick-release block perfectly matches the inner cross-sectional shape of the T-shaped quick-release slot, i.e., the upper cross-sectional width of the quick-release block is greater than the lower cross-sectional width, forming a T-shaped profile. During assembly, the operator aligns the quick-release block with the inlet section of the T-shaped quick-release slot and pushes it in one direction. The narrow section of the quick-release block slides along the inlet section into the bottom of the locking section. When it reaches the bottom, the tapered pin of the elastic locking pin automatically springs into the corresponding locking hole on the side of the quick-release block under the thrust of a miniature compression spring, completing the "push-and-lock" quick-release connection with perceptible mechanical feedback. The catheter tail connector 14 has an inflation port 15 and a Doppler signal output port 16 on its side. The inflation port 15 is a standard medical Luer connector, located in the proximal region of the side of the catheter tail connector 14, used to directly connect to a standard interface syringe or miniature liquid pump in emergency situations without additional adapters. The Doppler signal output port 16 is a miniature coaxial connector, whose shielding shell is soldered to the grounded copper foil inside the catheter tail connector 14 to isolate external electromagnetic interference. The catheter tail connector 14 extends rearward and is fixedly connected to a small-diameter multi-lumen catheter 17. The connection between the two is that the tail end of the small-diameter multi-lumen catheter 17 is inserted into the inner hole of the tail end of the catheter tail connector 14 and then pressed and fixed by a silicone sealing ring and a locking nut, forming a reliable connection interface that can withstand axial tensile force. At the same time, the catheter tail connector 14 and the small-diameter multi-lumen catheter 17 are pre-assembled as a single unit in the sterilized packaging.

[0038] The thin-diameter multi-lumen catheter 17 is made of medical-grade silicone material through a precision mold in a single extrusion process. Its overall outer diameter does not exceed eight millimeters, and its length is available in three adjustable sizes to suit different body types. The cross-section of the thin-diameter multi-lumen catheter 17 contains three independent, parallel, and non-interconnected channels: the main working channel 21 is located in the central area of ​​the cross-section, while the air-filled fluid channel 22 and signal line channel 23 are located on either side of the main working channel 21. The partitions between the three channels have uniform wall thickness, and the precise tolerance control of the extrusion mold ensures that the channels will not deform or interconnect when the catheter is bent. The main working channel 21 runs the entire length of the thin-diameter multi-lumen catheter 17, with its front end opening at the distal end face of the catheter and its rear end directly connected to the central opening of the catheter tail connector 14. In the non-perfusion state, this channel is idle; when needed, it can be used as a fluid pathway to deliver warm saline solution into the uterine cavity. The front end of the inflation fluid channel 22 is connected to the inner cavity of the elastic support capsule 18. This connection is achieved by opening a side hole on the outer wall of the front end of the narrow-diameter multi-lumen catheter 17 at a position corresponding to the outlet of the inflation fluid channel 22. Fluid within the inflation fluid channel 22 enters and exits the inner cavity of the elastic support capsule 18 through this side hole. The tail end of the inflation fluid channel 22 is connected to the inflation interface 15 via a corresponding pipe inside the catheter tail connector 14. The signal line channel 23 is used to pass through the shielded signal line of the integrated miniature Doppler probe 19. The shielded signal line travels from the upper surface of the elastic support capsule 18 along the inside of the narrow-diameter multi-lumen catheter 17 through the signal line channel 23 to the inside of the catheter tail connector 14, where it is soldered to the terminal of the Doppler signal output interface 16. There are no interruptions along the entire route to ensure the integrity and signal-to-noise ratio of the weak ultrasonic frequency shift signal during transmission. The front end of the thin-diameter multi-lumen catheter 17 is provided with an integrally injection-molded hemispherical silicone buffer head 25. The hemispherical silicone buffer head 25 is made of the same material as the body of the thin-diameter multi-lumen catheter 17, but with a slightly lower Shore hardness to increase the softness of the front end. When the catheter is inserted through the vagina and cervical canal, the buffer head 25 first contacts the birth canal mucosa and disperses the concentrated pressure of the axial thrust onto a larger spherical surface area, thereby protecting the tissue from scratches. The outer wall of the thin-diameter multi-lumen catheter 17 is provided with a corrugated anti-slip section 26 at a set distance from the front end. The corrugated anti-slip section 26 is composed of multiple equally spaced annular ridges arranged along the axial direction of the catheter. Each ridge is a continuous circular ring that is uniformly raised on the outer wall surface of the catheter. When the thin-diameter multi-lumen catheter 17 is pushed to the cervical canal, the corrugated anti-slip section 26 generates increased contact friction resistance between the cervical canal mucosal wall and the cervical canal, thereby helping to prevent the catheter from passively slipping due to the reaction force of the capsule expansion during the filling operation.

[0039] The elastic lifting capsule 18 is the core functional component of the device, fixed to the outer periphery of the front end of the narrow-diameter multi-lumen catheter 17. The elastic lifting capsule 18 is made of medical-grade high-elasticity silicone, with an elongation at break of not less than 500% to ensure that it does not undergo permanent plastic deformation or local rupture under repeated elastic deformation conditions of fluid inflation and pressure from the presenting part of the fetus. The capsule wall of the elastic lifting capsule 18 is a uniformly thin wall, and its root is heat-sealed to the outer wall of the front end of the narrow-diameter multi-lumen catheter 17 at a certain distance from the distal end using medical-grade silicone adhesive. The overlap width of the adhesive interface ensures sealing strength and anti-peeling performance. When not filled with fluid, the elastic lifting capsule 18 is in a naturally contracted state, tightly adhering to the outer wall of the front end of the narrow-diameter multi-lumen catheter 17, with its maximum outer diameter not exceeding the outer diameter of the narrow-diameter multi-lumen catheter 17 by a large margin, facilitating insertion through the vagina and cervical canal. After warm, sterile saline solution is injected through the inflation fluid channel 22, the sac wall expands under hydraulic pressure along a pre-set flat, elliptical disc-shaped contour: the upper surface forms a shallow concave arc surface to conform to the anatomical contour of the presenting part of the fetus, while the lower surface remains flat, facing away from the cervix. The upper surface of the elastic support sac 18 is provided with multiple radial drainage grooves 27, which radiate radially from the geometric center of the upper surface of the elastic support sac 18 to the edge of the sac. Each radial drainage groove 27 has a shallow concave arc-shaped cross-section. When the elastic support sac 18 expands and its upper surface contacts and adheres to the presenting part of the fetus, amniotic fluid and secretions can be guided and discharged from the center of the contact interface to the periphery of the sac along the radial drainage grooves 27, preventing fluid accumulation and the formation of a fluid film that could cause slippage between the sac and the presenting part of the fetus. The elastic support sac 18 has two symmetrical umbilical cord protection notches 28 on its edge. Each notch 28 has a semi-circular concave profile, allowing the prolapsed umbilical cord to pass through without being squeezed by the sac edge when it emerges from the support area. An integrated miniature Doppler probe 19 is embedded at the geometric center of the shallow concave arc surface on the upper surface of the elastic support sac 18. The outer periphery of the integrated miniature Doppler probe 19 is sealed and fixed within a corresponding groove on the sac surface by a silicone sealing ring 29. The silicone sealing ring 29 and the sac silicone material are integrally vulcanized and bonded, maintaining a seal without delamination or leakage under the elastic fatigue environment of repeated expansion and contraction of the sac. The acoustic window of the integrated miniature Doppler probe 19 faces upwards from the upper surface of the elastic support sac 18. When the sac expands and its upper surface contacts and adheres to the presenting part of the fetus, the acoustic window closely adheres to the tissue interface, emitting an ultrasound beam and receiving frequency-shifted echo signals from the umbilical artery blood flow.

[0040] The outer wall of the thin-diameter multi-lumen catheter 17 has a colored graduated ring extending posteriorly from the base of the self-elastic lifting capsule 18. The colored graduated ring is made of medical-grade silicone colored pigment and is screen-printed circumferentially along the outer wall of the thin-diameter multi-lumen catheter 17 to form continuous ring-shaped color segments. One color segment is placed every five millimeters, and from the base of the self-elastic lifting capsule 18 backwards, the segments are red, yellow, green, and blue in sequence. The colored graduated ring constitutes a visible indicator of the lifting height. During catheter insertion, the operator can directly observe the color segment of the graduated ring corresponding to the position of the external cervical os to intuitively determine the current effective lifting height.

[0041] A control display box is fixedly mounted on the side of the detachable self-locking base 1 via a snap-fit ​​mechanism. The control display box integrates a microcontroller, a rechargeable lithium battery, a Bluetooth module, a display screen, an audio amplifier module, and a miniature speaker. The microcontroller is a low-power embedded processor with an on-chip analog-to-digital converter (ADC) module and a serial communication interface. The ADC module of the microcontroller is connected to the shielded signal line led out from the integrated miniature Doppler probe 19 via the Doppler signal output interface 16 through a signal conditioning circuit to receive the ultrasonic frequency shift analog signal. The microcontroller's internal firmware contains a real-time blood flow audio demodulation algorithm, which converts the time-domain frequency shift signal into a frequency-domain blood flow velocity power spectrum based on a sliding window fast Fourier transform. Let the sampling sequence of the sliding window be a discrete signal with sampling point index n. A Hanning window function of length N is used to weight the truncated signal segment. The weighted signal segment is then subjected to a radix-2 decimation-time Fast Fourier Transform to obtain the complex spectrum at each frequency point. The distribution of the modulus of the complex spectrum with respect to frequency constitutes the blood flow velocity power spectrum at that window moment. The microcontroller uses the frequency value corresponding to the amplitude peak in the power spectrum as the instantaneous blood flow frequency shift peak. Simultaneously, the complete power spectrum data is reconstructed into an audible audio waveform of the blood flow frequency band through inverse short-time Fourier transform and envelope detection. The microcontroller outputs this blood flow audio waveform to an audio amplifier module via a digital-to-analog converter. The audio amplifier module drives a miniature speaker to play the umbilical artery blood flow audio signal in real time. The display screen is connected to the display driver interface of the microcontroller, and the blood flow velocity peak, intracystic pressure, and battery level information are refreshed in real time. The Bluetooth module connects to the serial communication interface of the microcontroller, wirelessly transmitting blood flow audio envelope data, intracystic pressure values, and device operating status data to an external receiving terminal. A miniature air pump inside the control display box connects to the inflation interface 15 via a silicone hose. The microcontroller's universal input / output interface controls the start / stop and speed of the miniature air pump through a drive circuit. The compressed gas output from the miniature air pump acts on the warm, sterile saline solution in the inflation fluid channel 22, driving the warm, sterile saline solution into the inner cavity of the elastic support cyst 18 for inflation. A pressure sensor is located within the inflation fluid passage of the elastic support cyst 18, near the cyst body end of the inflation fluid channel 22. The signal output of the pressure sensor is connected to the analog-to-digital converter module of the microcontroller, providing real-time intracystic pressure feedback values ​​to the microcontroller to form a closed-loop pressure monitoring system.

[0042] In this embodiment, the emergency deployment phase begins first. After diagnosing umbilical cord prolapse, the transport nurse opens the fixed arm 2 and movable arm 4 of the detachable self-locking base 1 next to the transport bed. The nurse then inserts the fixed arm 2 and movable arm 4 into the standard metal side rail approximately 30-40 cm from the perineum. The quick-clamping handle 6 is then flipped upwards. The involute cam surface at the front end of the quick-clamping handle 6 presses against the end face of the fixed arm 2, generating a cam thrust. This cam thrust drives the movable arm 4 to swing and close around the integrated pin 3 towards the fixed arm 2. During the closing process of the fixed arm 2 and movable arm 4, the arc-shaped anti-slip rubber pad is compressed and deformed to fully conform to the outer surface of the side rail. When the quick-clamping handle 6 is flipped to the dead center position, the cam thrust reaches its maximum value and forms a self-locking state after passing the dead center. At this point, the entire detachable self-locking base 1 is securely clamped onto the side rail. Next, the operator holds the ball head 12 with one hand and manually rotates it in the inner cavity of the damping washer 11 to adjust it so that the opening direction of the quick-release slot seat 13 is roughly aligned with the vaginal opening of the mother. After releasing the hand, the radial compressive force applied to the surface of the ball head 12 by the high elasticity silicone material of the damping washer 11 is converted into static friction torque, so that the ball head 12 remains locked at that angle.

[0043] Then, the pre-packaged and ethylene oxide-sterilized disposable insertion module assembly is removed from the sterilized packaging. Holding the catheter tail connector 14, the quick-release block on its side is aligned with the inlet section of the T-shaped quick-release slot on the quick-release slot seat 13 and pushed in a straight line in the direction of the arrow. The narrow section of the quick-release block slides along the inlet section into the bottom of the locking section. When the quick-release block slides to the bottom of the locking section, the conical pin of the elastic locking pin automatically springs into the corresponding locking hole on the side of the quick-release block under the pushing force of the micro compression spring, completing the mechanical locking. Turn on the power switch of the control display box. After the micro microcontroller initializes the various peripheral modules, the display screen starts up. The display interface sequentially displays the real-time battery capacity percentage, the current reading of the bladder internal pressure, and the standby heart rate indicator icon.

[0044] The insertion and repositioning phase then begins. The operator uses their left index and middle fingers to guide the catheter along the vagina to the external cervical os, establishing a tactile reference point. With their right hand, they hold the middle section of the thin-diameter multi-lumen catheter 17 and align its tip with the vaginal opening. During insertion, the hemispherical silicone buffer head 25 first contacts the vaginal mucosa. Its soft, spherical shape distributes the concentrated pressure of the axial thrust over a larger contact area. The silicone material on the outer wall of the thin-diameter multi-lumen catheter 17 naturally curves and conforms to the anatomical curvature of the birth canal. Once the tip of the catheter 17 enters the cervical canal, the multiple annular ridges of the corrugated anti-slip section 26 increase frictional damping against the cervical canal mucosa. The operator can perceive a slight change in pushing resistance, thus determining that the catheter tip has entered the cervical canal. Insertion continues while continuously observing the depth of the colored graduated ring on the external segment. Insertion is stopped when the green segment of the colored ring aligns with the external cervical os. At this point, the base of the elastic support capsule 18 is positioned slightly inside the external cervical os. The operator uses a syringe to draw warm, sterile saline solution, inserts the syringe tip into the Luer connector of the inflation port 15, and tightens it to form a sealed connection. The operator then slowly pushes the syringe piston to allow the saline solution to enter the inner cavity of the elastic support sac 18 along the inflation fluid channel 22. Under hydraulic pressure, the sac wall gradually unfolds from its contracted state into a flat, elliptical, pre-set shape within the uterine cavity. The shallow concave arc surface of the upper surface gradually rises and conforms to the hemispherical contour of the presenting part of the fetus, while the lower surface remains flat and stable, facing away from the cervix. During the inflation process, the display screen of the control box refreshes in real time the intracystic pressure value, which is collected by the pressure sensor and calculated by the microcontroller after analog-to-digital conversion. The operator dynamically controls the injection volume of the syringe based on the display screen readings. After inflation is complete, the microcontroller converts the ultrasound frequency shift analog signal received from the integrated micro Doppler probe 19 via the Doppler signal output interface 16 into an analog-to-digital signal and runs a real-time blood flow audio demodulation algorithm to window the discrete signal sequence within the sampling window. The windowing formula is as follows:

[0045]

[0046] The original sampled signal sequence x[n] is a time-domain signal containing blood flow frequency shift components, received and amplified by the integrated miniature Doppler probe 19, where n is the sampling point index, w[n] is the Hanning window sequence, and N is the total number of sampling points within a single sliding window. The weighted signal segment is then subjected to a radix-2 decimation-time fast Fourier transform to obtain the frequency domain complex spectrum X[k].

[0047]

[0048] Where k is the frequency domain sampling point index, and X[k] is the discrete Fourier transform complex value of the k-th frequency point. The microcontroller calculates the modulus value of each frequency point and takes the frequency corresponding to the maximum modulus value as the instantaneous blood flow frequency shift peak. At the same time, the microcontroller reconstructs the complete power spectrum into an audible audio waveform of the blood flow in the audio frequency band through short-time Fourier inverse transform and Hilbert envelope detection, and outputs it to the audio power amplifier module to drive the micro speaker after digital-to-analog conversion. When the speaker emits a continuous and regular "whooshing" sound with a rhythm synchronized with the maternal heart rate, it can be determined that the umbilical artery blood flow has been restored and the umbilical cord compression has been relieved.

[0049] After confirming the restoration of umbilical cord blood flow, the process enters the locking, fine-tuning, and transport maintenance phase. The operator gently adjusts the angle of the thin-diameter multi-lumen catheter 17 within the birth canal by manually adjusting the ball head 12, ensuring that the catheter 17 follows the natural anatomical curvature from the vagina to the cervix in a compliant posture without lateral stress. Upon releasing the hand, the static friction torque applied by the damping washer 11 to the ball head 12 keeps the catheter 17 stable and undeflected in this optimal posture. At this time, the elastic lifting sac 18 expands, lifting the presenting part of the fetus upward away from the internal cervical os. The weight of the presenting part exerts downward pressure on the upper surface of the sac. The elastic tension of the sac wall and the hydraulic pressure within the sac combine to form a reaction force that balances this downward pressure. The sac maintains a stable lifting height under dynamic equilibrium. The radial drainage grooves 27 on the upper surface of the elastic support sac 18 form multiple radial drainage channels within the contact interface between the sac and the presenting part of the fetus. Amniotic fluid and secretions, under the combined action of gravity and internal pressure within the sac, continuously drain from the center of the contact interface to the edge of the sac along the radial drainage grooves 27, maintaining a dry and close fit at the support interface. The prolapsed umbilical cord naturally exits through the umbilical cord protection notch 28 at the edge of the elastic support sac 18, and blood flow within the umbilical cord is not mechanically compressed by the edge of the sac. The acoustic window of the integrated micro Doppler probe 19, after the sac expands, adheres tightly to the surface of the presenting part of the fetus, continuously emitting a continuous ultrasound beam with a frequency center at four MHz towards the umbilical artery region and receiving the frequency-shifted echoes generated by the reflections of flowing red blood cells within the umbilical artery. The frequency-shifted echo signal is transmitted via a shielded signal line along the signal line channel 23 inside the thin-diameter multi-lumen catheter 17 to the Doppler signal output interface 16, entering the control and display box. The micro-microcontroller continuously runs a real-time blood flow audio demodulation algorithm to convert the frequency-shifted signal into audio output in real time. At this point, the operator can completely release their hands, and the mother, in the Trendelenburg position, is transferred by transport bed through the corridor and elevator to the operating room. Throughout the transfer, a miniature speaker continuously outputs an audio signal of umbilical artery blood flow. Any member of the surgical team can judge the continuity of umbilical cord perfusion by the presence or absence of this audio signal and its rhythmic changes. If the intensity of the blood flow audio signal weakens or the rhythm becomes discontinuous during the transport, the accompanying personnel can immediately use a syringe to inject a small amount of warm sterile saline through the inflation port 15 to fine-tune the lifting height. The additional saline enters the elastic lifting sac 18 along the inflation fluid channel 22, slightly increasing the sac's inflated height and further lifting the presenting part away from the internal cervical os, thereby restoring the patency of umbilical artery blood flow. When the miniature speaker re-transmits a continuous and regular blood flow audio signal after the additional injection, it indicates that the umbilical cord compression has been relieved again.

[0050] If ultrasound assessment indicates insufficient amniotic fluid volume and the umbilical cord faces the risk of dry compression due to insufficient amniotic fluid buffering during transport or waiting in the operating room, the operator can connect an extension tube of a micro-infusion pump to the central opening of the catheter tail connector 14, which is directly connected to the rear end of the main working channel 21. The micro-infusion pump drips warm, sterile saline into the uterine cavity at a set low rate through the front opening of the main working channel 21, replenishing amniotic fluid volume and improving the suspension and buffering environment of the umbilical cord within the uterine cavity. The main working channel 21 is an idle channel when not being used for irrigation, and the irrigation operation does not interfere with the lifting function of the elastic lifting sac 18 or the pressure maintenance of the inflation fluid channel 22.

[0051] After completing preoperative disinfection, draping, and anesthesia preparation in the operating room, the withdrawal phase begins. The assistant uses a syringe to aspirate all the saline solution from the inner cavity of the elastic support capsule 18 through the inflation port 15. Under the action of high elastic recovery force, the capsule wall contracts from its flat, elliptical, disc-shaped expansion state back to its initial state, tightly adhering to the outer wall of the front end of the narrow-diameter multi-lumen catheter 17. Then, the operator gently lifts the catheter tail connector 14, smoothly withdrawing the entire narrow-diameter multi-lumen catheter 17 from the vagina along the opposite direction of the insertion path. Pressing the release button of the elastic locking pin causes the tapered pin to overcome the thrust of the micro-compression spring and disengage from the locking hole on the side of the quick-release block. The quick-release block of the catheter tail connector 14 slides out of the T-shaped quick-release slot of the quick-release slot seat 13 along the direction of the insertion section, completing the separation of the insertion module from the anchoring module. The narrow-diameter multi-lumen catheter 17, the elastic support capsule 18, and the integrated micro-Doppler probe 19 are discarded as disposable sterile consumable components in a medical waste collection container. The separable self-locking base 1 and ball joint connector 9 are disinfected by soaking and wiping with chlorine-containing disinfectant and then stored for reuse in the next emergency.

[0052] Throughout the transfer and waiting process, the Bluetooth module integrated within the control display box continuously transmits the blood flow audio envelope data processed by the microcontroller, the intracystic pressure value, the battery percentage, and the device operating status flag data wirelessly to the central monitoring display terminal at the nursing station in the form of Bluetooth Low Energy protocol data packets. Based on the received data, the central monitoring display terminal renders and displays in real time on the software interface a spectral waterfall graph of umbilical artery blood flow audio, a trend curve of intracystic pressure changing over time, and the remaining battery power of the device. It also sets up an alarm rule engine to trigger a red warning pop-up and audible and visual alarms for events such as loss of blood flow audio signals exceeding a set time or an abnormal drop in intracystic pressure from the baseline value.

[0053] This embodiment integrates a bed rail self-anchoring structure, a universal self-locking posture maintenance structure, and a non-stuffing elastic lifting structure into a device for umbilical cord prolapse reduction and irrigation maintenance. The device is securely clamped to the side rail of the transport bed via a detachable self-locking base. After catheter insertion and sac filling, the operator can immediately release their hands to participate in other emergency procedures, fundamentally changing the traditional working mode where umbilical cord prolapse emergency care relies on continuous manual pushing. The elastic lifting sac, with its controllable expansion height at the tip of a thin-diameter multi-lumen catheter, gently lifts the presenting part away from the internal cervical os without occupying the main volume of the uterine cavity or altering the overall tension of the uterine wall. This greatly ensures the safety of intrauterine instrument operations during labor and avoids the risk of uterine rupture that may be caused by abnormal tension on the uterine wall due to suffocation-style expansion. A miniature Doppler probe integrated into the geometric center of the elastic support capsule collects umbilical artery blood flow frequency shift signals in real time and converts them into audible audio output through a real-time blood flow audio demodulation algorithm. This allows medical personnel to instantly confirm the umbilical cord perfusion status by hearing during transport, avoiding the judgment delays caused by relying solely on fetal heart rate monitoring after traditional manual reduction and the physiological time lag in fetal heart rate changes. A universal friction self-locking mechanism between the ball joint connector and the damping washer enables rapid adjustment of the catheter's approach direction and maintains the posture by locking upon release, ensuring a stable and unwavering support position even under bumpy transport conditions. A color-coded graduated ring provides a visual indication of the support height without the need for a power source, allowing operators to visually read the current effective support height under any lighting conditions and with electronic devices in operation. The entire device transforms umbilical cord prolapse emergency care from a physically dependent manual operation to a standardized, self-maintaining operation, significantly improving the safety and ease of operation during emergency transport and reducing the physical burden on operators.

[0054] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit it. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solutions of the present invention without departing from the spirit and scope of the present invention, and all such modifications or substitutions should be covered within the scope of the claims of the present invention.

Claims

1. An integrated device for umbilical cord prolapse reduction and perfusion maintenance, characterized in that: The device includes a detachable self-locking base. A fixed clamping arm is fixedly mounted at the lower end of the detachable self-locking base. A movable clamping arm is hinged to the fixed clamping arm via an integrated pin. A quick-clamping handle is connected to the tail end of the movable clamping arm via a flip shaft. A ball joint connector is bolted to the upper end of the detachable self-locking base. A ball joint connector has a ball head embedded in its inner cavity. A quick-release slot is fixedly mounted on the top of the ball head. A catheter tail connector is detachably connected to the quick-release slot. The catheter tail connector extends rearward and is fixedly connected to a small-diameter multi-lumen catheter. An elastic support capsule is heat-sealed to the outer periphery of the front end of the small-diameter multi-lumen catheter. An integrated micro Doppler probe is embedded in the upper surface of the elastic support capsule. A control display box is fixedly mounted on the side of the detachable self-locking base. The control display box contains a micro Doppler probe. The control and display box is connected via circuitry to the integrated micro Doppler probe, a pressure sensor located within the fluid-filled passage of the elastic support sac, and a micro air pump that pumps warm, sterile saline solution into the elastic support sac through the inflation port. The elastic support sac is inflated with warm, sterile saline solution through the fluid-filled passage to lift the presenting part of the fetus away from the internal cervical os, relieving umbilical cord compression. The micro Doppler adaptively adjusts the output of the micro air pump based on the real-time feedback of the sac's internal pressure from the pressure sensor, ensuring stable internal pressure and lifting height of the elastic support sac under transport bumps and fluctuations in the presenting part's gravity. The integrated micro Doppler probe acquires the umbilical artery blood flow frequency shift signal in real time and demodulates it into an audio output by the micro Doppler to confirm the umbilical cord perfusion status.

2. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The ball joint connector includes a hemispherical seat and a damping washer embedded in the cavity of the hemispherical seat, with the ball head embedded in the cavity of the damping washer.

3. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The quick-release slot is a T-shaped quick-release slot, which consists of an upper inlet section and a lower locking section. The locking section is equipped with an elastic locking pin, which is composed of a miniature compression spring and a tapered pin. The side of the conduit tail connector is integrally provided with a quick-release block. The outer cross-section of the quick-release block matches the inner contour of the T-shaped quick-release slot. When the quick-release block is pushed into the bottom of the locking section, the tapered pin automatically springs into the corresponding locking hole. The slot is unlocked when the release button of the elastic locking pin is pressed.

4. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The catheter tail connector is provided with an inflation port and a Doppler signal output port on its side. The inflation port is a Luer connector and the Doppler signal output port is a coaxial connector.

5. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The cross-section of the narrow-diameter multi-lumen catheter has three independent parallel channels: a main working channel, an inflation fluid channel, and a signal line channel. The main working channel runs through the entire length of the narrow-diameter multi-lumen catheter and its front end opens at the distal end face of the narrow-diameter multi-lumen catheter. The front end of the inflation fluid channel is connected to the inner cavity of the elastic support bladder and its tail end is led out through the inflation interface. The signal line channel is used to pass through the shielded signal line of the integrated micro Doppler probe.

6. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The upper surface of the elastic support bag is a shallow concave arc surface, the lower surface of the elastic support bag is a flat surface, the upper surface of the elastic support bag is provided with multiple radial drainage grooves, and the edge of the elastic support bag is provided with two symmetrical umbilical cord protection notches.

7. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 6, characterized in that: The integrated micro Doppler probe is embedded at the geometric center of the shallow concave arc surface on the upper surface of the elastic support capsule. The outer periphery of the integrated micro Doppler probe is sealed and fixed by a silicone sealing ring. The acoustic window of the integrated micro Doppler probe faces upwards from the upper surface of the elastic support capsule.

8. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The outer wall of the narrow-diameter multi-lumen catheter is provided with a colored scale ring from the root of the elastic support bladder to the rear, and the colored scale ring is provided with a color segment every five millimeters.

9. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The front end of the narrow-diameter multi-lumen conduit is provided with an integrally injection-molded hemispherical silicone buffer head, and the outer wall of the narrow-diameter multi-lumen conduit is provided with a corrugated anti-slip section composed of multiple annular convex lines at a set distance from the front end.

10. The integrated device for umbilical cord prolapse reduction and perfusion maintenance according to claim 1, characterized in that: The control and display box integrates a microcontroller, a rechargeable lithium battery, a Bluetooth module, a display screen, an audio amplifier module, and a micro speaker. The microcontroller receives the frequency shift signal from the integrated micro Doppler probe and outputs it to the audio amplifier module to drive the micro speaker to play the umbilical artery blood flow audio signal in real time. Furthermore, based on the deviation between the intracystic pressure fed back by the pressure sensor in real time and the set target lifting intracystic pressure, the microcontroller adaptively controls the start, stop, and speed of the micro air pump through a closed-loop adjustment algorithm, so that the lifting intracystic pressure of the elastic lifting bladder dynamically converges to the target lifting intracystic pressure. The microcontroller is embedded with a real-time blood flow audio demodulation algorithm and a closed-loop adjustment algorithm. The real-time blood flow audio demodulation algorithm uses a sliding window of length N to capture the frequency shift signal of the integrated micro Doppler probe. After weighting the discrete signal sequence within the window using the Hanning window function, a fast Fourier transform is performed to obtain the blood flow velocity power spectrum, and the frequency corresponding to the peak value of the power spectrum amplitude is taken as the instantaneous blood flow frequency shift peak value. The closed-loop adjustment algorithm adjusts the output of the micro air pump in conjunction with the instantaneous blood flow frequency shift peak value and the intracystic pressure fed back by the pressure sensor to maintain the stability of the umbilical artery perfusion index.

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