A transparent detection device for visualizing leaks in aortic surgery

Abstract

The utility model discloses a kind of transparent detection devices for visualization leak detection in aortic surgery, including hollow circular truncated cone or conical transparent shell, its proximal end is provided with opening, opening outside is formed in proper order with bandage shoulder platform and annular cantilever lip, and soft sealing ring is set between the two, to adhere aortic root outer wall and realize annular sealing by suture or bandage. Water inlet, exhaust port and pressure measuring port are set along the same annular height of shell side wall, all adopt luer interface. Pressure measuring port can be detachably connected with pressure measuring assembly, and the pressure measuring assembly includes the connecting structure sealed with interface, the extension line rod extended along the inner cavity of shell and the end pressure sensor, and display screen and button are set on the shell, to realize pressure real-time monitoring. The device has reliable sealing, visualization perfusion and accurate degassing, real-time pressure measurement and other functions, improve aortic repair surgery in water leakage determination accuracy and operation efficiency.

Description

Technical Field

[0001] This utility model belongs to the field of medical devices, specifically relating to a transparent detection device for visual leak detection during aortic surgery. Background Technology

[0002] With the continuous development of cardiovascular surgery techniques, surgeries related to the aortic root and aortic valve are gradually increasing. Procedures such as aortic valve repair, aortic root replacement, and valve annulus repair all require reliable intraoperative assessment of aortic valve closure and the sealing of aortic root sutures. Currently, clinical practice mainly relies on observing for leakage after saline perfusion or intracardiac pressurization to determine suture integrity and leaflet occlusion. Traditional methods typically use a syringe with a simple container to manually establish pressure through perfusion, allowing direct observation of blood or perfusion fluid extravasation under the surgical field. However, this method is highly dependent on sealing conditions, easily introduces air bubbles during perfusion, and is difficult to achieve stable air removal. Air bubble rise and local water flow disturbance can easily interfere with judgment. Furthermore, perfusion pressure is usually controlled empirically, lacking real-time, objective pressure monitoring methods, making it impossible to quantitatively record and alert on perfusion pressure, thus posing a risk of misjudgment.

[0003] Furthermore, existing detection methods often employ conventional cylindrical or film-wrapped methods to seal the aortic root. These methods struggle to conform well to the irregular vessel walls, requiring surgeons to hold the device manually or use temporary sutures for fixation. Uneven sealing can lead to localized leakage, resulting in inaccurate detection or requiring repeated repairs. Some devices have simple venting structures, failing to effectively guide and centrally expel air bubbles, causing residual gas buildup and affecting the clarity of the observation interface. Other solutions lack independent pressure measurement channels and dedicated interfaces, hindering stable connections to professional pressure monitoring modules and impeding multi-point simultaneous intraoperative operations. Overall, current technologies still have limitations in stable sealing, air bubble drainage, perfusion interface placement, and reliable pressure monitoring, making it difficult to balance operational efficiency, intuitive observation, and accurate results. Therefore, there is an urgent need for a structurally sound, reliably sealed intraoperative auxiliary tool with effective degassing and standardized pressure detection capabilities to improve the leakage assessment process after aortic repair and valve repair, enhancing the accuracy and consistency of intraoperative assessments. Utility Model Content

[0004] This invention addresses the shortcomings of existing technologies by providing a transparent detection device for visual leak detection during aortic surgery. It effectively solves the problems of insufficient sealing stability, inadequate venting, and difficulty in intuitively grasping the pressure status during the sealing and perfusion detection of the aortic root during surgery.

[0005] The technical solution adopted by this utility model to solve the above problems is as follows: A transparent detection device for visual leak detection during aortic surgery includes a transparent shell, which is a hollow frustum or cone structure with an opening at the proximal end. A band shoulder and a circumferential cantilever lip are sequentially formed on the outer side of the opening away from the opening. A soft sealing ring is provided on the outer periphery of the transparent shell between the band shoulder and the circumferential cantilever lip for adhering to the outer wall of the aortic root and sealing by sutures or circumferential tightening of the band at the band shoulder. The sidewall of the transparent shell is provided with a water inlet, an air outlet and a pressure measuring port along the same circumferential height. The outer ends of the water inlet, air outlet and pressure measuring port are all provided with external threaded joints for Luer-type connection. The exhaust port is equipped with a one-way valve assembly and a bubble-drawing assembly, and the one-way valve assembly includes a duckbill valve body. The bubble-guiding assembly includes an annular air-gathering shoulder formed inside the exhaust port, and at least two bubble-guiding ribs are provided upward from the annular air-gathering shoulder along the height direction of the shell to guide the rising bubbles to the exhaust port. The pressure testing port is detachably connected to the pressure testing assembly. The pressure testing assembly includes a connection structure that seals with the pressure testing port, an extension rod extending along the inner cavity of the housing, and a pressure sensor disposed at the distal end of the extension rod. A display screen and buttons are disposed on the outer housing of the pressure testing assembly.

[0006] Preferably, the external threaded connector has a Luer external thread structure, and the outer end of the vent is also provided with a detachable sealing cap.

[0007] Preferably, the connection structure includes an internal threaded mounting sleeve, which is detachably connected to the external threaded connector at the outer end of the pressure testing port by means of threads, for locking and sealing the pressure testing component at the pressure testing port.

[0008] Preferably, the bubble-drawing assembly is disposed in the lower part of the inner cavity of the exhaust port, and the annular gas-collecting shoulder has an upwardly inclined arc surface or a stepped structure, which is used to collect the bubbles rising along the shell and guide them to the center of the exhaust channel. The bubble guide ribs are evenly distributed along the inner wall of the transparent shell, with a quantity of 3 to 6 ribs. Each bubble guide rib starts from the annular gas collecting shoulder and gradually extends towards the exhaust port. The top spacing is less than 1 / 5 of the inner diameter of the exhaust port, so as to form a stable upward airflow channel and improve the bubble gathering efficiency when the liquid flows.

[0009] Preferably, the water inlet, vent, and pressure measuring port are distributed at equal angles along the circumference of the shell, and are spaced apart from each other at 120°±15°.

[0010] Preferably, the soft sealing ring is made of medical-grade silicone rubber with a Shore A hardness of 40-50.

[0011] Preferably, the transparent shell is made of transparent medical polycarbonate or transparent medical copolyolefin material.

[0012] Preferably, the pressure measuring component has a closed electronic cavity inside, which integrates a pressure signal acquisition chip, a microprocessor circuit and a power supply unit. The power supply unit includes a rechargeable battery encapsulated in the cavity. A through wiring groove is provided between the electronic cavity and the extension rod, and a wire channel is provided in the extension rod to electrically connect the pressure sensor and the pressure signal acquisition chip. The outer surface of the pressure measuring component is equipped with a display screen for pressure value and alarm information prompts, as well as buttons for mode switching, zeroing and alarm threshold adjustment, and a charging interface is provided on the side of the housing. The pressure measuring component has an annular sealing lip at its front end, which is located behind the internal threaded mounting sleeve and is used to form a liquid seal with the edge of the pressure measuring port when tightened.

[0013] This utility model has a novel structure, ingenious design, and is simple and convenient to operate. Compared with the prior art, it has the following advantages: 1. This utility model utilizes a hollow, frustum-shaped or conical transparent shell, with a strap shoulder and a circumferential cantilever lip structure formed on the outer side of the opening. Combined with a soft outer sealing ring, this achieves a close fit and reliable circumferential sealing against the outer wall of the aortic root. An injection port, an vent port, and a pressure measuring port are located at the same circumferential height on the side wall of the shell, each using a Luer threaded connector, providing independent operating channels for injection, venting, and pressure measurement. The vent port contains a one-way valve assembly and a ring-shaped air-collecting shoulder-bubble-guiding rib structure to guide bubbles to rise and exit unidirectionally. A pressure measuring assembly can be detachably connected to the pressure measuring port, allowing the pressure sensor to penetrate deep into the shell cavity. Readings and mode adjustments are made via an external display and buttons, thus enabling visual assessment of injection pressure and leakage conditions, combined with the transparent material.

[0014] 2. Compared to existing methods that rely on manual temporary sealing or ordinary containers for perfusion, this invention provides a tissue adhesion and fixation interface through a collaborative structure of shoulder platform-cantilever lip-sealing ring, resulting in a more uniform and stable seal and reducing the risk of localized leakage and misjudgment caused by uneven force or unstable handling. Simultaneously, the side wall interfaces are arranged at equal angles and equipped with threaded locking connections, making the perfusion, venting, and pressure measurement operation paths clear and the operation more standardized, reducing tubing interference and surgical field confusion, and facilitating smooth completion of the examination process within the confined thoracic cavity.

[0015] 3. This utility model further utilizes an integrated annular air-gathering shoulder and multiple bubble-guiding ribs within the exhaust port to allow air bubbles to converge upwards along a defined flow line and bead-type one-way valve for discharge, reducing the interference of residual air bubbles on the observation interface; simultaneously, the pressure measuring component extends the pressure sensor to a position close to the test chamber, and through a microprocessor circuit and display device, it realizes real-time pressure display and threshold adjustment, making it easier for the operator to obtain more intuitive and objective perfusion pressure information, and improving the accuracy and consistency of the judgment on the sealing of the aortic root and the closure of the valve leaflets. Attached Figure Description

[0016] Figure 1 This is an isometric view of the first state of this utility model.

[0017] Figure 2 This is an isometric view of the second state of this utility model.

[0018] Figure 3 This is an internal isometric view of the present invention.

[0019] Figure 4 This is an isometric view of the interior of the exhaust port of this utility model.

[0020] Figure 5 This is an isometric view of the pressure measuring component of this utility model.

[0021] In the attached diagram: 1-Transparent shell, 2-Opening, 3-Strap shoulder, 4-Cantilever lip, 5-Soft sealing ring, 6-Water inlet, 7-Exhaust port, 8-Pressure testing port, 9-Pressure testing assembly, 10-Bubble initiation assembly, 11-One-way valve assembly, 12-Sealing cap, 13-External threaded connector, 14-Annular air intake shoulder, 15-Bubble guide rib, 16-Duckbill valve body, 17-Internal threaded mounting sleeve, 18-Display screen, 19-Button, 20-Extension rod, 21-Pressure sensor. Detailed Implementation

[0022] The following are specific embodiments of the present invention, and the technical solution of the present invention will be further described in conjunction with the accompanying drawings. However, the present invention is not limited to these embodiments.

[0023] like Figure 1-5As shown, this utility model provides a transparent detection device for visual leak detection during aortic surgery, comprising a transparent shell 1, a sealing structure, a three-port functional interface system, and a pressure measurement component 9 for pressure acquisition. The transparent shell 1 is generally hollow frustum or conical in shape, and its geometric shape facilitates conforming to the shape of the aortic root and concentrates pressurized fluid, ensuring the formation of a stable observation cavity inside. Preferably, the height of the transparent shell 1 is 30mm to 60mm, and the opening diameter ranges from 25mm to 45mm, to adapt to the common adult aortic root diameter (approximately 26mm-38mm). The transparent shell 1 can be injection molded from transparent medical polycarbonate (PC) or transparent medical copolyolefin (COC), with a thickness of approximately 1.0mm to 2.0mm. These materials have good optical transmittance (≥90%), biocompatibility, and crack resistance, meeting the visual requirements and structural strength requirements during surgical use. The shell is shaped like a cone or frustum, which creates a uniform pressure transmission surface for the liquid from bottom to top inside, making it easier for doctors to observe the location of leaks.

[0024] The transparent shell 1 has an opening 2 at its proximal end. A strap shoulder 3 and a circumferential cantilever lip 4 are formed sequentially on the outer side of the opening away from it. The strap shoulder 3 forms a regular annular stepped surface, serving as a support platform for suture fixation or strap tightening. Its width is preferably 2mm to 5mm to facilitate reliable suturing and positioning in situations with limited surgical visibility. The circumferential cantilever lip 4 is located distal to the strap shoulder 3, with its outer edge forming a downward-curving short side structure to assist in anti-slipping, preventing the device from easily shifting or rotating after fixation. A soft sealing ring 5 is provided between the strap shoulder 3 and the cantilever lip 4. The sealing ring is preferably made of medical-grade silicone rubber with a Shore A hardness of 40 to 50, providing stable fit and elastic pressure without damaging tissue. The height of the sealing ring 5 can be set to 4mm to 8mm, forming a continuous sealing band between the ring and the outer wall of the aortic root, thus preventing leakage, displacement, and buffering tissue friction.

[0025] The transparent shell 1 has an injection port 6, an vent port 7, and a pressure measuring port 8 at the same circumferential height on its sidewall, with an angle of 120°±15° between each port. This three-port structure avoids multi-layer overlap, facilitating rapid intraoperative identification and zoning. Each port end has an external thread connector 13, using a standard Luer connection (generally a 6% taper standard Luer thread), compatible with standard medical infusion tubing, allowing for rapid assembly with syringes, infusion tubing, check valve assemblies, and other accessories. The thread length is approximately 6mm~10mm, ensuring connection stability and liquid sealing. The injection port 6 is used for perfusion of physiological saline or simulated blood, the vent port 7 is used to expel air bubbles, and the pressure measuring port 8 is used for pressure acquisition. This three-channel separation reduces interference during simultaneous surgical procedures and avoids accidental contact or tubing crossing that could lead to difficulties in judgment.

[0026] A one-way valve assembly 11 is installed inside the exhaust port 7. The one-way valve assembly 11 includes a duckbill-type valve body 16. The valve body is preferably made of medical-grade elastomer material (such as medical-grade silicone rubber or TPU elastomer). The valve disc thickness is set to 0.2mm~0.5mm. It has low opening pressure (less than 1kPa) and rebound sealing characteristics, which can prevent external gas or liquid from flowing back into the device cavity and ensure stable infusion pressure. An bubble-guiding assembly 10 is also provided inside the exhaust port 7, including an annular gas-collecting shoulder 14 and at least two bubble-guiding ribs 15. The annular gas-collecting shoulder 14 is located in the inner cavity of the housing near the exhaust port. Its inner surface can be an upwardly inclined arc surface or a stepped shape, with an inclination angle preferably 5°~20°. It is used to collect the tiny bubbles floating with the liquid flow and make them slide towards the exhaust port 7. The bubble guide ribs 15 are evenly distributed along the inner wall of the shell, preferably 3 to 6 in number. The cross-section can be semi-circular or wedge-shaped, with a width of 1mm to 3mm and a height of 1mm to 4mm. They extend from the annular gas collecting shoulder 14 to the exhaust port 7. Under liquid disturbance, they maintain the directionality of bubble flow, prevent bubbles from scattering and floating or sticking to the wall, and improve degassing efficiency and observation clarity.

[0027] The pressure measuring port 8 is used to install the pressure measuring assembly 9. The pressure measuring assembly 9 includes a connecting structure that seals with the pressure measuring port, an extension rod 20, and a pressure sensor 21 located at the front end. The connecting structure uses an internally threaded mounting sleeve 17, which engages with the externally threaded connector 13 to achieve locking and liquid sealing. An annular sealing lip is provided inside the internally threaded mounting sleeve 17, which forms a liquid-tight interface with the edge of the pressure measuring port 8 after being pressed. The sealing lip width is 0.5mm to 2mm to prevent leakage of the perfusion liquid along the thread. The extension rod 20 extends into the cavity beyond the wall thickness of the housing. The rod diameter is preferably 2mm to 3.5mm, so that the pressure sensor 21 is close to the center of the liquid to obtain a more stable pressure reading. The pressure sensor 21 can be a miniature strain gauge or MEMS piezoresistive sensor, with a recommended range of 0 to 300 mmHg and an accuracy within ±2 mmHg to adapt to the simulated pressure range of cardiac surgery perfusion. The pressure sensing component housing houses a sealed electronic cavity containing a pressure signal acquisition chip, a microprocessor unit, and a rechargeable battery. Externally, it features a display screen 18 and buttons 19, enabling real-time pressure display, zero-point calibration, and threshold alarm adjustment. The electronic component connects to the pressure sensor 21 via wiring channels and extension rods 20. A Type-C or magnetic charging interface can be provided on the side of the housing for easy charging before surgery, reducing the frequency of disassembly and assembly.

[0028] The overall structure allows the device to establish intraoperative intraluminal pressure via manual or syringe pump perfusion. The surgeon can observe the suture site for fluid leakage through the transparent shell, while the pressure monitoring component collects the perfusion pressure value in real time. Combined with the venting channel and bubble guide structure, continuous venting and visual field maintenance are achieved, solving the problems of unstable operation, inaccurate pressure sensing, and bubble interference in judgment caused by traditional temporary occlusion methods. The transparent shell and sealing area structure avoid concentrated compression of aortic tissue, and the three-port distribution allows perfusion, venting, and monitoring to be performed simultaneously. The entire device can be packaged in disposable aseptic packaging to avoid the risk of cross-infection. The manufacturing process, including injection molding, insert vulcanization sealing ring, silicone valve molding, electronic component packaging, and assembly testing, can be carried out by existing medical device production systems.

[0029] Furthermore, such as Figure 1-4 As shown, the external threaded connector 13 adopts a standard Luer external thread interface, with its taper designed according to conventional medical connection specifications (e.g., a 6% taper standard). The preferred thread pitch is 0.7mm to 1.2mm, and the threaded length is approximately 6mm to 10mm. It is compatible with commonly used clinical Luer lock connectors, infusion tubing, or syringe ports, enabling a quick and stable connection between the infusion tubing and the venting channel. To prevent accidental leakage or liquid spillage from ports not currently in use during surgery, a detachable sealing cap 12 is provided at the outer end of the venting port 7. A flat or annular sealing ring can be provided on the inner side of the sealing cap 12, achieving a tight seal through threaded compression. This allows for pre-layout of the liquid infusion and venting path during the surgical preparation phase, ensuring flexible, safe, and reliable operation.

[0030] The connection structure includes an internally threaded mounting sleeve 17, which is detachably connected to the externally threaded connector 13 at the outer end of the pressure measuring port 8 via threads. The thread engagement length is preferably not less than 5 mm to ensure a strong connection and sealing capability. An annular sealing lip, preferably 0.5 mm to 2 mm wide, is provided at the bottom of the mounting sleeve 17. After the threads are tightened, the sealing lip adheres to the edge surface of the pressure measuring port 8 to form a liquid seal. This structure facilitates repeated disassembly and assembly without damaging the housing structure. It can be quickly removed when the pressure monitoring component needs replacement or postoperative treatment, meeting the requirements for disposable or detachable modular medical devices.

[0031] In terms of degassing structures, such as Figure 4As shown, the bubble-guiding assembly 10 is arranged in the lower end region of the inner cavity of the exhaust port 7. The annular gas-collecting shoulder 14 is preferably designed as an upwardly inclined arc surface or a stepped zigzag shape, with an inclination angle of 5° to 20°, so that the bubbles in the inner cavity can still naturally converge along the inclined surface under liquid disturbance, avoiding the random dispersion of bubbles on the curved surface of the shell and affecting visual judgment. The outer edge of the gas-collecting shoulder 14 transitions smoothly with the inner wall of the shell, avoiding gas accumulation or flow resistance in the sharp turning area. The bubble-guiding ribs 15 are evenly distributed circumferentially along the inner wall of the shell 1, with a number of 3 to 6. Their cross-section can be semi-circular, rectangular, or wedge-shaped, with a width of about 1mm to 3mm, and protruding 1mm to 4mm above the inner wall of the shell. They extend from the gas-collecting shoulder 14 towards the exhaust port 7 and terminate at a distance of 0.3mm to 0.8mm from the inner edge of the exhaust port, so that when the liquid flows, an upward guiding flow field is formed locally, and the bubbles generate a "slippery band effect" along the surface of the bubble-guiding ribs and rise rapidly to be discharged. The spacing between the tops of each bubble guide rib is less than 1 / 5 of the inner diameter of the exhaust port, which can form a multi-point, diverted bubble channel, reduce the risk of single-channel blockage, and improve exhaust efficiency and the clarity of the observation interface.

[0032] Through the above structural arrangement, continuous and directional air bubble drainage can be achieved during the venting process. Compared with the traditional method of relying solely on natural upward venting, this structure enhances the degassing effect through geometric guidance without introducing additional power. This eliminates the need for frequent container adjustments or manual venting during operation, reducing the probability of air bubbles obscuring the valve opening and suture area, thereby improving the stability of intraoperative judgment and the accuracy of observation.

[0033] Furthermore, the dimensions, angles, and processing techniques of each component can be achieved through one-time injection molding combined with a secondary silicone sleeve. Manufacturing precision within ±0.1mm is sufficient to meet functional requirements, facilitating mass production. The bubble guide ribs and air intake shoulders can be integrally molded within the mold structure, reducing additional assembly steps. Overall assembly can utilize conventional cleanroom manufacturing processes for medical devices, including injection molding, silicone encapsulation, component insertion, seal testing, and EO sterilization packaging, making large-scale implementation easy.

[0034] Furthermore, such as Figure 1-3 As shown, to achieve a reasonable perfusion flow path arrangement, a neat observation field, and convenient instrument operation, the water inlet 6, vent 7, and pressure measuring port 8 are arranged at equal angles along the circumference of the housing, with an interval of 120°±15°. This layout, by evenly distributing the interface positions, ensures that the paths for perfusion fluid entry, gas discharge, and pressure signal acquisition do not interfere with each other, avoiding local pressure fluctuations, fluid turbulence, or tubing entanglement caused by the concentration of these three on one side. It maintains a stable fluid filling state inside the housing, achieving a uniform flow field and continuous venting effect. The three ports are located on the upper side wall area of ​​the housing, allowing for flexible adjustment of the connector direction according to the clinical surgical field space, which is beneficial for the surgeon's field of vision and instrument access planning, and avoids obstruction of the aortic valve orifice and suture area.

[0035] The soft sealing ring 5 is preferably made of medical-grade silicone rubber with a Shore A hardness of 40-50 and a thickness of 1mm-3mm. This hardness range allows for sufficient compression deformation when the suture or band is tightened, thus conforming to the irregular outer wall of the blood vessel and forming a continuous annular seal. It is less prone to seal slippage or local lifting due to residual pressure from cardiac pulsation or the thrust of perfusion fluid. The sealing ring 5 can be integrally molded or attached to the outer wall of the transparent shell 1, forming a stable limit with the band shoulder 3. This eliminates the need for the surgeon to manually hold the ring or repeatedly adjust the sealing position, making the intraoperative operation more standardized and reproducible.

[0036] The transparent shell 1 is preferably made of transparent medical-grade polycarbonate (PC) or transparent medical-grade copolyolefin material, with a wall thickness preferably between 1 mm and 3 mm, to balance good mechanical strength and optical transmittance. Polycarbonate material has an optical transmittance of ≥85%, excellent impact resistance, and can withstand operating table operations and changes in irrigation pressure; copolyolefin material combines flexibility, crack resistance, and good biocompatibility. Both can be injection molded, and mold precision control within ±0.1 mm is sufficient to meet the requirements for sealing fit and display interface clarity. The outer surface of the shell can be selectively treated with an anti-fog coating or have a hydrophilic coating added to prevent localized water droplets from interfering with vision when covered by irrigation fluid, thus facilitating clear imaging of the valve leaflet contact line and suture points.

[0037] Through the above-mentioned materials and structural arrangement, a comprehensive detection structure is formed that is stable and fits well, has a clear field of vision, and does not interfere with the pipeline. It not only meets the requirements of intraoperative pressure environment and repeated perfusion, but also is compatible with medical sterilization process and clinical operation procedure, and facilitates the switching between mass production and single-use or multiple sterilization use modes.

[0038] Furthermore, such as Figure 5 As shown, to achieve real-time acquisition and display of perfusion pressure, the pressure measuring component 9 has a sealed electronic cavity inside. The electronic cavity preferably uses a medical-grade sealed injection-molded shell structure, and its inner wall can be reinforced with 0.2mm to 0.5mm ribs to improve structural strength and vibration resistance. The electronic cavity integrates a pressure signal acquisition chip, microprocessor circuit, and power supply unit. It preferably uses a low-power medical-grade microprocessor chip, supporting a pressure measurement range of 0–300 mmHg with a measurement resolution of 0.1 mmHg, meeting the requirements of aortic perfusion detection for capturing fine pressure changes. The power supply unit uses a rechargeable lithium battery encapsulated within the cavity, with a typical capacity of 150mAh to 300mAh, ensuring stable power supply while maintaining continuous operation for ≥4 hours. The charging interface is located on the outer shell of the pressure measuring component 9 and is not connected to the fluid circuit, facilitating preoperative charging and maintenance.

[0039] To ensure a reliable connection between the pressure sensor 21 and the circuitry within the electronic cavity, a through wiring groove is provided between the electronic cavity and the extension rod 20. A straight or slightly curved wire channel, with a width and depth of 0.8mm to 1.5mm, is formed within the extension rod 20 to accommodate the insulated wire and prevent backflow of the injection liquid. The pressure sensor 21 is located at the distal end of the extension rod 20, close to the internal space of the transparent housing 1, allowing direct contact with the injection liquid and real-time reflection of injection pressure changes. The sensor encapsulation employs epoxy sealing or medical-grade silicone coating to ensure signal stability and waterproof performance under long-term immersion conditions; a waterproof rating of ≥IPX7 is preferred.

[0040] The pressure measuring component 9 has a display screen 18 and buttons 19 on its outer surface. The display screen 18 is preferably a 0.6-inch to 1.2-inch low-power OLED or LCD screen, used to display real-time pressure values, peak pressures, and status icons. The font height is recommended to be ≥4mm to accommodate the surgical field observation distance. The buttons 19 are used for mode switching, zeroing, and alarm threshold adjustment. They can be mechanical waterproof buttons or membrane touch buttons, providing clear mechanical feedback or visual cues to facilitate sterile glove operation during surgery. The system supports preoperative zeroing, allowing the pressure sensor 21 to be placed in a pressure-free state for benchmark calibration before installation, improving measurement accuracy.

[0041] Furthermore, to ensure sealing and anti-detachment performance after connection with the pressure testing port 8, an annular sealing lip is provided at the front end of the pressure testing component 9. The sealing lip is made of an elastomer material with a typical thickness of 0.5mm to 1.2mm and is located behind the internal threaded mounting sleeve 17. During installation, the operator tightens the pressure testing component 9 onto the external threaded connector 13 through the internal threaded mounting sleeve 17. Under the action of axial clamping force, the annular sealing lip fits against the edge of the pressure testing port 8 to achieve a liquid seal. This achieves a pressure resistance requirement of ≥25kPa without relying on auxiliary sealing components, preventing leakage of the infusion fluid or backflow of air. This structure allows for quick installation and disassembly, making it suitable for intraoperative temporary pressure testing and surgical procedure switching scenarios, enhancing the flexibility and safety of the device.

[0042] Through the aforementioned electronic sealing structure, sensor wiring method, and liquid-tight interface design, real-time and stable pressure monitoring and threshold alarm capabilities can be provided without interfering with the perfusion pathway and observation field of view. This significantly improves the objectivity and repeatability of the intraoperative perfusion assessment process in aortic surgery, thereby supporting standardized and regulated intraoperative judgment procedures.

[0043] like Figure 1-5As shown, when using this device, ① after the surgeon completes the aortic root suture repair operation, the opening 2 of the transparent shell 1 is aligned with the aortic root cut end and fitted downwards, so that the soft sealing ring 5 is circumferentially attached to the outer wall of the aortic root. Then, sutures or medical bands are used to fix it around the shoulder 3 to ensure that a stable sealing interface is formed between the transparent shell 1 and the aortic root, and the cantilever lip 4 is close to the tissue edge to avoid local shear damage; ② the syringe or infusion tubing is connected to the water inlet 6 through the external threaded connector 13, and the sealing cap 12 of the vent 7 is opened, or connected to the external drainage tubing, so that the one-way valve assembly 11 is in a state of unobstructed venting passage, and the infusion fluid is started to flow. During the infusion process, the air bubbles are concentrated and floated upwards under the guidance of the bubble guide rib 15 and the annular air collection shoulder 14 and exit from the vent 7. Drain until the transparent shell 1 is filled with liquid and the liquid is continuously drained, then close the sealing cap 12; ③ Screw the pressure measuring component 9 onto the pressure measuring port 8, so that the inner threaded mounting sleeve 17 and the outer threaded connector 13 are screwed together, and the annular sealing lip is axially pressed to achieve a liquid seal. The extension rod 20 and the pressure sensor 21 enter the shell cavity to complete the pressure measurement preparation. Press the button 19 to start the device and zero it. Then, gradually inject the irrigation fluid to build up the pressure. Observe the pressure curve and value in real time through the display screen 18 and judge the suture tightness and valve alignment status in combination with the liquid leakage in the transparent shell 1. When the pressure reaches the range set by the surgeon or when abnormal leakage occurs, stop pressurizing and make necessary suture adjustments or supplementary repairs according to the display and visual observation results. After the test is completed, disassemble in reverse and clean the surgical area with physiological saline.

[0044] The specific embodiments described herein are merely illustrative examples illustrating the spirit of this utility model. Those skilled in the art to which this utility model pertains may make various modifications or additions to the described specific embodiments or use similar methods to replace them, without departing from the spirit of this utility model or exceeding the scope defined by the appended claims.

Claims

1. A transparent detection device for visual leak detection during aortic surgery, comprising a transparent housing (1), characterized in that: The transparent shell (1) is a hollow frustum or cone structure with an opening (2) at the proximal end. A strap shoulder (3) and a circumferential cantilever lip (4) are formed sequentially on the outer side of the opening (2) away from the opening (2). A soft sealing ring (5) is provided on the outer periphery of the transparent shell (1) between the strap shoulder (3) and the circumferential cantilever lip (4) for attaching to the outer wall of the aortic root and sealing it by sutures or circumferential tightening of the strap at the strap shoulder (3). The sidewall of the transparent shell (1) is provided with a water inlet (6), an air outlet (7) and a pressure measuring port (8) along the same circumferential height. The outer ends of the water inlet (6), the air outlet (7) and the pressure measuring port (8) are provided with external threaded joints (13) for Luer-type connection. The exhaust port (7) is equipped with a one-way valve assembly (11) and a bubble-drawing assembly (10), the one-way valve assembly (11) including a duckbill valve body (16). The bubble-guiding assembly (10) includes an annular air-gathering shoulder (14) formed within the exhaust port (7), and at least two bubble-guiding ribs (15) are provided upward from the annular air-gathering shoulder (14) along the height direction of the shell to guide the floating bubbles to the exhaust port (7). The pressure measuring port (8) is detachably connected to the pressure measuring assembly (9). The pressure measuring assembly (9) includes a connection structure that seals with the pressure measuring port (8), an extension rod (20) extending along the inner cavity of the housing, and a pressure sensor (21) disposed at the far end of the extension rod (20). A display screen (18) and buttons (19) are provided on the outer housing of the pressure measuring assembly (9).

2. The transparent detection device for visual leak detection during aortic surgery according to claim 1, characterized in that, The external threaded connector (13) has a Luer external thread structure, and the outer end of the vent (7) is also provided with a detachable sealing cap (12).

3. A transparent detection device for visual leak detection during aortic surgery according to claim 2, characterized in that, The connection structure includes an internal threaded mounting sleeve (17), which is detachably connected to the external threaded connector (13) at the outer end of the pressure measuring port (8) by means of threads, for locking and sealing the pressure measuring component (9) at the pressure measuring port (8).

4. A transparent detection device for visual leak detection during aortic surgery according to claim 1, characterized in that, The bubble-drawing assembly (10) is located in the lower part of the inner cavity of the exhaust port (7). The annular gas-collecting shoulder (14) has an upwardly inclined arc surface or a stepped structure, which is used to collect the bubbles rising along the shell and guide them to the center of the exhaust channel. The bubble guide ribs (15) are evenly distributed along the inner wall of the transparent shell (1) in a circumferential direction, with a quantity of 3 to 6. Each bubble guide rib (15) starts from the annular gas gathering shoulder (14) and gradually extends towards the exhaust port (7). The top spacing is less than 1 / 5 of the inner diameter of the exhaust port (7) so as to form a stable upward airflow channel and improve the bubble gathering efficiency when the liquid flows.

5. A transparent detection device for visual leak detection during aortic surgery according to claim 1, characterized in that, The water inlet (6), vent (7) and pressure measuring port (8) are distributed at equal angles along the circumference of the shell, with a spacing of 120°±15° between them.

6. A transparent detection device for visual leak detection during aortic surgery according to claim 1, characterized in that, The soft sealing ring (5) is made of medical silicone rubber with a hardness of Shore A 40-50.

7. A transparent detection device for visual leak detection during aortic surgery according to claim 1, characterized in that, The transparent shell (1) is made of transparent medical polycarbonate or transparent medical copolyolefin material.

8. A transparent detection device for visual leak detection during aortic surgery according to claim 3, characterized in that, The pressure measuring component (9) has a closed electronic cavity inside, which integrates a pressure signal acquisition chip, a microprocessor circuit and a power supply unit. The power supply unit includes a rechargeable battery encapsulated in the cavity. A through wiring groove is provided between the electronic cavity and the extension rod (20). A wire channel is provided inside the extension rod (20) to electrically connect the pressure sensor (21) and the pressure signal acquisition chip. The outer surface of the pressure measuring component (9) is provided with a display screen (18) for pressure value and alarm information prompts, and buttons (19) for mode switching, zeroing and alarm threshold adjustment, and a charging interface is provided on the side of the housing; The pressure measuring component (9) has an annular sealing lip at its front end. The annular sealing lip is located on the rear side of the internal threaded mounting sleeve (17) and is used to form a liquid seal with the edge of the pressure measuring port (8) when it is tightened.

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