Artery indwelling needle

Abstract

The invention discloses an artery indwelling needle, which belongs to the technical field of medical treatment, and comprises a joint and a catheter which are communicated with each other, the silica gel plug is arranged at the joint of the joint and the catheter; the pipe sealing liquid storage cavity is formed in the connector, and a first fluid channel is arranged between the pipe sealing liquid storage cavity and the connector in a communicating mode. According to the artery indwelling needle, the dynamic pressure balance cavity, the pressure sensitive piston, the communicating cavity, the balloon and the movable plate are arranged, catheter sealing operation and needle withdrawing action are synchronously completed, catheter blockage caused by manual operation delay is avoided, the artery indwelling needle is particularly suitable for patients needing long-term catheter indwelling, no open pipeline operation exists in the whole process, and the operation is convenient. The pre-filling sterile design of the tube sealing liquid cavity is combined, the incidence rate of related blood flow infection is effectively reduced, the whole process from blood drawing completion to tube sealing liquid injection does not need to disassemble an injector, switch a valve or manually connect the tube sealing liquid, the operation steps are reduced from traditional four steps to one step, and the operation time is effectively shortened.

Description

Technical Field

[0001] The invention relates to the field of medical technology, and in particular to an arterial indwelling needle. Background Art

[0002] In clinical medicine, arterial catheters are important medical devices for long-term infusion or long-term monitoring of arteries. The core requirement is to ensure that the access is unobstructed, prevent blood reflux and thrombosis, and reduce the risk of infection. During the use of traditional indwelling catheters, medical staff need to manually complete the tube sealing operation after blood drawing, that is, inject sealing liquid (such as saline, sodium heparin solution) through a syringe to flush the catheter and maintain the patency of the lumen.

[0003] Manual tube sealing must strictly follow the push-stop-push pulse operation specifications to ensure that the sealing liquid forms turbulence in the catheter and fully replaces the blood. It requires multiple operating steps such as disassembling the syringe, switching the valve or manually connecting the sealing liquid. The operation is cumbersome and may lead to untimely tube sealing. In the process of connecting the pipeline, it is easy to contact with the outside world, causing infection in the internal pipeline. Summary of the invention

[0004] The purpose of the present invention is to provide an arterial indwelling needle, which is used to solve the technical problems in the prior art that the tube is not sealed in time and is easily contacted with the outside world during the process of connecting the pipeline, resulting in infection of the internal pipeline.

[0005] In order to achieve the above object, the present invention provides the following technical solution: an arterial indwelling needle, comprising:

[0006] Connectors and conduits provided for communication;

[0007] A silicone plug, which is provided at the connection between the connector and the catheter;

[0008] The tube sealing liquid storage chamber is provided inside the joint and is connected with the joint to form a first fluid passage;

[0009] A pressure-responsive channel switching unit, comprising:

[0010] A dynamic pressure balance chamber is disposed in the joint and is connected to the conduit to adjust the air pressure change in the dynamic pressure balance chamber in real time;

[0011] A pressure sensitive piston is slidably disposed in the dynamic pressure balance chamber, and its displacement responds in real time to the change of the air pressure in the dynamic pressure balance chamber;

[0012] A puncture assembly, comprising a moving plate and a puncture needle, wherein the moving plate is rigidly connected to the pressure-sensitive piston;

[0013] A communication chamber, which is connected to the first fluid passage;

[0014] A balloon, which is arranged in a communication cavity and fills the communication cavity to block the first fluid passage;

[0015] The pressure-responsive channel switching unit includes the following states:

[0016] When the syringe is inserted into the silicone plug for blood drawing and the air pressure in the dynamic pressure balance cavity reaches the first threshold value, the pressure-sensitive piston moves to drive the moving plate to drive the puncture needle to pierce the balloon, and the first fluid passage is temporarily blocked by the moving plate;

[0017] After the syringe is withdrawn, the negative pressure in the catheter is eliminated, and the pressure-sensitive piston moves reversely under the drive of the negative pressure difference in the dynamic pressure balance cavity, driving the moving plate to reset and open the first fluid passage, and based on the pressure difference between the residual negative pressure in the communication cavity and the sealing liquid storage cavity, the sealing liquid is automatically released into the catheter.

[0018] Preferably, the first fluid passage includes a liquid outlet passage, a moving groove and a liquid discharge passage. The liquid outlet passage is communicatively arranged between the moving groove and the main passage. The moving plate is slidably arranged in the moving groove, and when the moving plate resets, it scratches the inlet of the liquid outlet passage to form a transient negative pressure, accelerating the sealing liquid to enter the catheter.

[0019] Preferably, the liquid discharge passage is communicatively arranged between the sealing liquid storage cavity and the communication cavity. The liquid discharge passage includes a first acceleration passage, a second acceleration passage and a third acceleration passage which are communicatively arranged in sequence, and the cross-sectional area of the three decreases from the liquid inlet to the liquid outlet.

[0020] Preferably, spherical cavities are arranged at the joints of the first acceleration passage, the second acceleration passage and the third acceleration passage, and a negative pressure suction passage is communicatively arranged between adjacent two spherical cavities.

[0021] Preferably, hydrophobic membranes are arranged at both ports of the negative pressure suction passage so that only gas can pass through the negative pressure suction passage.

[0022] Preferably, a first air passage is communicatively arranged between the dynamic pressure balance cavity and the catheter. A second air passage is communicatively arranged between the first air passage near the air inlet port and the communication cavity, and a hydrophobic membrane is arranged at the connection port of the second air passage and the communication cavity.

[0023] Preferably, an elastic membrane is arranged at the connection port of the first air passage and the catheter. A through hole is opened at the center position of the elastic membrane, and gaps are evenly distributed around the through hole to automatically adjust the size of the through hole according to the change of the negative pressure in the catheter.

[0024] Preferably, the liquid outlet passage is inclined, and the liquid outlet port is lower than the liquid inlet port.

[0025] Preferably, a filter screen is arranged at the liquid inlet port of the liquid outlet passage.

[0026] Preferably, a duckbill valve is provided in the main channel of the connector, and the opening faces the direction of the catheter.

[0027] In the above technical solution, an arterial indwelling needle provided by the present invention has the following beneficial effects:

[0028] In the present invention, through the provided dynamic pressure balance chamber, pressure-sensitive piston, communication chamber, balloon and moving plate, when the syringe is inserted into the silicone plug for blood drawing, when the air pressure in the dynamic pressure balance chamber reaches the first threshold, the pressure-sensitive piston moves to drive the moving plate to drive the puncture needle to pierce the balloon, and the first fluid passage is temporarily closed by the moving plate. After the syringe is withdrawn, the negative pressure in the catheter is eliminated, and the pressure-sensitive piston moves reversely under the drive of the negative pressure difference in the dynamic pressure balance chamber, driving the moving plate to reset and open the first fluid passage, and based on the pressure difference between the residual negative pressure in the communication chamber and the sealant storage chamber, the sealant is automatically released into the catheter. The sealing operation and the needle-pulling action are completed synchronously, avoiding catheter blockage caused by human operation delay, especially suitable for patients who need long-term catheterization, and there is no open pipeline operation throughout the process. Combined with the pre-filled aseptic design of the sealant chamber, the incidence of related bloodstream infections is effectively reduced, and there is no need to disassemble the syringe, switch valves or manually connect the sealant from the completion of blood drawing to the injection of the sealant. The operation steps are reduced from the traditional four steps to one step, effectively shortening the operation time. Description of the Drawings

[0029] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the following will briefly introduce the drawings required for use in the embodiments. Obviously, the drawings described below are only some embodiments recorded in the present invention. For those of ordinary skill in the art, other drawings can also be obtained based on these drawings.

[0030] Figure 1 A three-dimensional view provided by an embodiment of the present invention;

[0031] Figure 2 A front sectional structure schematic diagram provided by an embodiment of the present invention;

[0032] Figure 3 An enlarged structure schematic diagram of part A provided by an embodiment of the present invention;

[0033] Figure 4 An enlarged structure schematic diagram of part C provided by an embodiment of the present invention;

[0034] Figure 5 An enlarged structure schematic diagram of part E provided by an embodiment of the present invention;

[0035] Figure 6 An enlarged structure schematic diagram of part B provided by an embodiment of the present invention;

[0036] Figure 7 A schematic diagram of the enlarged structure of point D provided in an embodiment of the present invention;

[0037] Figure 8 A schematic diagram of an enlarged structure of D after deformation provided by an embodiment of the present invention;

[0038] Figure 9 A schematic diagram of an initial state of an elastic membrane provided by an embodiment of the present invention;

[0039] Figure 10 This is a schematic diagram of the elastic membrane in a deformed state according to an embodiment of the present invention.

[0040] Description of reference numerals:

[0041] 1. Connector; 2. Catheter; 3. Side hole; 4. Silicone plug; 5. Sealing liquid storage chamber; 6. Side tube; 7. Balloon; 8. Dynamic pressure balance chamber; 9. Pressure sensitive piston; 10. Liquid outlet channel; 11. Moving groove; 12. Moving plate; 13. Needle; 14. Liquid discharge channel; 141. First acceleration channel; 142. Second acceleration channel; 143. Third acceleration channel; 15. Elastic membrane; 16. Connecting chamber. DETAILED DESCRIPTION

[0042] In order to enable those skilled in the art to better understand the technical solution of the present invention, the present invention will be further described in detail below with reference to the accompanying drawings.

[0043] like Figure 1-10 As shown, an arterial indwelling needle comprises:

[0044] A connector 1 and a conduit 2 are connected and arranged;

[0045] A silicone plug 4 is provided at the connection between the connector 1 and the conduit 2;

[0046] The sealing liquid storage chamber 5 is provided inside the connector 1 and is connected to the connector 1 to form a first fluid passage;

[0047] A pressure-responsive channel switching unit, comprising:

[0048] A dynamic pressure balance chamber 8 is disposed in the joint 1 and is connected to the conduit 2 to adjust the air pressure change in the dynamic pressure balance chamber 8 in real time;

[0049] A pressure sensitive piston 9 is slidably disposed in the dynamic pressure balance chamber 8, and its displacement responds to the change of the air pressure in the dynamic pressure balance chamber 8 in real time;

[0050] The puncture assembly includes a moving plate 12 and a puncture needle 13, wherein the moving plate 12 is rigidly connected to the pressure sensitive piston 9;

[0051] A communicating cavity 16, which is communicatively arranged on the first fluid passage;

[0052] A balloon 7, which is arranged in the communicating cavity 16 and fills the communicating cavity 16 to block the first fluid passage;

[0053] The pressure-responsive channel switching unit includes the following states:

[0054] When the syringe is inserted into the silica gel plug 4 for blood drawing and the air pressure in the dynamic pressure balance cavity 8 reaches the first threshold value, the pressure-sensitive piston 9 moves to drive the moving plate 12 to drive the puncture needle 13 to puncture the balloon 7, and temporarily closes the first fluid passage through the moving plate 12;

[0055] After the syringe is withdrawn, the negative pressure in the catheter 2 is eliminated, and the pressure-sensitive piston 9 moves in the reverse direction under the drive of the negative pressure difference in the dynamic pressure balance cavity 8, driving the moving plate 12 to reset and open the first fluid passage, and automatically releases the sealing liquid into the catheter 2 based on the pressure difference between the residual negative pressure in the communicating cavity 16 and the sealing liquid storage cavity 5.

[0056] Specifically, the arterial indwelling needle is inserted into the patient's artery, and the arterial indwelling needle is fixed on the patient's skin surface through medical tape, which is convenient for subsequent connection with various monitoring pipelines or infusion pipelines, and there is no need to repeatedly perform the needle insertion operation, thus reducing the harm caused to the patient by repeated needle punctures.

[0057] Further, when it is necessary to perform a blood drawing operation on the patient, through the silica gel plug 4 arranged in the side hole 3 on the outer wall of the joint 1 and communicated with the side tube 6 arranged on the catheter 2. During blood drawing, after disinfecting the needle of the syringe, it is directly inserted into the silica gel plug 4, so that the needle of the syringe is communicated with the catheter 2. Close the valve of the pipeline connection, and then perform the blood drawing operation through the syringe. It is not necessary to disassemble the pipeline and the joint 1 to realize the blood drawing operation, which is convenient and fast, further saving the disassembly steps of the pipeline and the joint 1, thus avoiding internal pipeline infection caused by repeated disconnection and connection, and improving the overall sealing performance of the pipeline through the arranged silica gel plug 4.

[0058] Further, since the inside of the catheter 2 is in a negative pressure state during blood drawing, when the negative pressure in the catheter 2 reaches a certain threshold during blood drawing, vascular collapse is likely to occur. By connecting the dynamic pressure balance chamber 8 and the catheter 2, and arranging the pressure-sensitive piston 9 in the dynamic pressure balance chamber 8, the dynamic pressure balance chamber 8 is divided into a first chamber near the interface of the connector 1 and a second chamber near the catheter 2. The catheter 2 is connected to the first chamber. When blood drawing is performed, since the inside of the catheter 2 is in a negative pressure state, the gas in the first chamber is sucked, thereby releasing part of the pressure in the catheter 2, so as to keep the negative pressure in the catheter 2 within the safe threshold range, effectively reducing the risk of vascular collapse during blood drawing, thereby improving the safety during blood drawing, reducing the incidence of medical accidents, and the entire blood drawing process is completed in a closed environment. It is not necessary to connect to the outside to keep the negative pressure in the catheter 2 within the safe threshold range, effectively avoiding the pollution of the internal environment.

[0059] Further, when blood drawing is performed, since the inside of the catheter 2 is in a negative pressure state, the gas in the first chamber is sucked, thereby releasing part of the pressure in the catheter 2. During the process, since the internal air pressure in the first chamber gradually decreases under the negative pressure suction of the catheter 2, the pressure-sensitive piston 9 responds in real time to the change of the internal air pressure in the first chamber. As the internal air pressure in the first chamber decreases, the pressure-sensitive piston 9 moves towards the interface of the connector 1, thereby reducing the internal volume of the first chamber to adapt to the change of the air pressure in the first chamber. The displacement of the pressure-sensitive piston 9 responds in real time to the change of the negative pressure in the first chamber. As the pressure-sensitive piston 9 moves, the connecting rod fixedly connected to the surface of the pressure-sensitive piston 9 close to the inside of the first chamber is driven to move synchronously, thereby driving the moving plate 12 fixedly connected to one end of the connecting rod to move synchronously towards the communicating chamber 16. When the air pressure in the first chamber reaches the first threshold, the pressure-sensitive piston 9 moves to drive the moving plate 12 to drive the puncture needle 13 to pierce the balloon 7 in the communicating chamber 16, and temporarily closes the first fluid passage through the moving plate 12. The communicating chamber 16 is filled with the balloon 7, which completely blocks the first fluid passage under normal conditions, preventing the sealing liquid from accidentally flowing into the blood vessel or blood backflow into the storage chamber, and avoiding the risks of drug contamination or blood backflow. After the blood drawing is completed and the syringe needle is withdrawn, due to the internal elastic force of the silicone plug 4 itself, the needle hole part is deformed and closed, so as to keep the inside of the arterial indwelling needle in a closed environment state all the time, and the whole operation is pollution-free.

[0060] Furthermore, after the syringe needle is pulled out, the negative pressure in the catheter 2 is eliminated. At this time, since the air pressure in the first chamber decreases when blood is drawn, the pressure-sensitive piston 9 moves toward the interface of the connector 1, thereby reducing the internal volume of the first chamber to adapt to the air pressure change in the first chamber, thereby increasing the internal volume of the second chamber. Since the amount of gas in the second chamber remains unchanged, the increase in volume causes negative pressure to be generated in the second chamber, and a negative pressure difference is generated with the first chamber. When the negative pressure in the catheter 2 is eliminated, the pressure-sensitive piston 9 is driven to move in the opposite direction by the negative pressure difference, thereby driving the movable plate 12 to move in the opposite direction synchronously and reset, thereby opening the first fluid passage, and based on the connecting chamber 16 The residual negative pressure inside and the positive pressure of the tube-sealing liquid storage chamber 5 form a pressure difference, which automatically releases the tube-sealing liquid to the catheter 2, thereby achieving accurate release of the tube-sealing liquid release dose, avoiding excessive release dose entering the blood vessel due to manual injection, and completing the tube-sealing operation and the needle removal action simultaneously, avoiding blockage of the catheter 2 due to manual operation delay. It is especially suitable for patients who need long-term catheterization, and there is no open pipeline operation throughout the process. Combined with the pre-filled aseptic design of the tube-sealing liquid chamber, the incidence of related bloodstream infection is effectively reduced. There is no need to disassemble the syringe, switch the valve or manually connect the tube-sealing liquid from the completion of blood drawing to the injection of the tube-sealing liquid. The operation steps are reduced from the traditional four steps to one step, effectively shortening the operation time.

[0061] As a further embodiment of the present invention, the first fluid passage includes a liquid outlet channel 10, a movable groove 11 and a liquid discharge channel 14. The liquid outlet channel 10 is connected between the movable groove 11 and the main channel. The movable plate 12 is slidably arranged in the movable groove 11. When the movable plate 12 is reset, it scratches the entrance of the liquid outlet channel 10 to form a transient negative pressure, thereby accelerating the sealing liquid to enter the catheter 2.

[0062] Specifically, the moving groove 11 is communicated with the communicating cavity 16. The inlet of the liquid outlet channel 10 is located on one side wall of the moving groove 11. And in the initial state, the moving plate 12 is located on the side of the inlet of the liquid outlet channel 10 far from the communicating cavity 16. At this time, the liquid outlet channel 10 is in communication with the communicating cavity 16, and the passage between the liquid outlet channel 10 and the liquid discharge channel 14 is blocked by the balloon 7 in the communicating cavity 16. When drawing blood, the movement of the pressure-sensitive piston 9 drives the connecting rod fixedly arranged on the surface of the pressure-sensitive piston 9 close to the first chamber to move synchronously, so as to drive the moving plate 12 fixedly connected to one end of the connecting rod to move synchronously in the moving groove 11 towards the communicating cavity 16. When the air pressure in the first chamber reaches the first threshold, the pressure-sensitive piston 9 moves to drive the moving plate 12 to drive the puncture needle 13 to puncture the balloon 7 in the communicating cavity 16. At this time, a pressure difference is formed by the positive pressure of the communicating cavity 16 and the sealing liquid storage cavity 5, and the sealing liquid is automatically released into the communicating cavity 16. And the moving plate 12 moves to the side of the inlet of the liquid outlet channel 10 close to the communicating cavity 16, so that the moving plate 12 blocks between the inlet of the liquid outlet channel 10 and the communicating cavity 16. Thus, when drawing blood, the sealing liquid in the communicating cavity 16 is temporarily blocked from flowing into the liquid outlet channel 10, so as to temporarily seal the first fluid passage.

[0063] Further, after the blood drawing is completed and the syringe needle is withdrawn, the negative pressure in the catheter 2 is eliminated, and the pressure-sensitive piston 9 is driven to move reversely by the negative pressure difference, so as to drive the moving plate 12 to move reversely and reset synchronously in the moving groove 11, so as to drive the moving plate 12 to move to the side of the inlet of the liquid outlet channel 10 far from the communicating cavity 16, so that the liquid outlet channel 10 is communicated with the communicating cavity 16 to open the first fluid passage. Thus, under the action of the pressure difference between the residual negative pressure in the communicating cavity 16 and the sealing liquid storage cavity 5, the sealing liquid is automatically released into the catheter 2 through the liquid outlet channel 10. Since when the moving plate 12 resets, it scratches the inlet of the liquid outlet channel 10 to form a transient negative pressure, accelerating the smooth entry of the sealing liquid into the catheter 2, thereby improving the stability of the automatic sealing system.

[0064] As a further embodiment provided by the present invention, the liquid discharge channel 14 is communicated between the sealing liquid storage cavity 5 and the communicating cavity 16. The liquid discharge channel 14 includes a first acceleration channel 141, a second acceleration channel 142 and a third acceleration channel 143 which are sequentially communicated, and the channel cross-sections of the three decrease from the liquid inlet to the liquid outlet.

[0065] Further, after blood collection is completed and the syringe needle is withdrawn, when the heparin flush solution is automatically released into the catheter 2, the heparin flush solution enters the communication cavity 16 through the drainage channel 14. Since the drainage channel 14 includes a first acceleration channel 141, a second acceleration channel 142, and a third acceleration channel 143 that are sequentially connected in communication, and the cross-sectional areas of the three channels decrease from the liquid inlet to the liquid outlet, following the principle that the flow velocity is small where the cross-sectional area is large and the flow velocity is large where the cross-sectional area is small, the heparin flush solution enters the drainage channel 14 and is sequentially accelerated through the first acceleration channel 141, the second acceleration channel 142, and the third acceleration channel 143 and then discharged into the communication cavity 16:

[0066] The first acceleration channel 141 (with a larger cross-sectional area) serves as the inlet, allowing the heparin flush solution to flow in smoothly;

[0067] The second acceleration channel 142 (with a medium cross-sectional area) increases the flow velocity;

[0068] The third acceleration channel 143 (with the smallest cross-sectional area) further maximizes the flow velocity, ensuring that the heparin flush solution quickly passes through the channel in a short time and avoiding blood backflow in the catheter 2 due to too slow a flow velocity.

[0069] Further, the pressure difference between the residual negative pressure in the communication cavity 16 and the heparin flush solution storage cavity 5 drives the drainage. Through the design of decreasing cross-sectional area, the sensitivity of the flow velocity to pressure changes can be amplified, enabling effective drainage even with a small pressure difference by increasing the flow velocity. The heparin flush solution is sequentially accelerated through the first acceleration channel 141, the second acceleration channel 142, and the third acceleration channel 143. The increase in flow velocity will cause the hydrostatic pressure to decrease. The high-speed flow in the first acceleration channel 141, the second acceleration channel 142, and the third acceleration channel 143 can form a step-by-step local negative pressure at the end of the channel, thereby successively generating a suction effect on the heparin flush solution storage cavity 5, the first acceleration channel 141, and the second acceleration channel 142, further promoting the outflow of the heparin flush solution, compensating for the possible insufficient pressure difference between the heparin flush solution storage cavity 5 and the communication cavity 16, ensuring the reliability of the drainage process, and thus improving the stability of the self-drainage system.

[0070] Further, the high-speed flow can reduce the residence time of the heparin flush solution in the channel, avoid blockage of the channel due to sedimentation of drug components during standing, and at the same time reduce the possibility of microbial colonization in the pipeline. The high-speed flowing heparin flush solution has a high momentum and can form a strong unidirectional flow during the drainage process, effectively offsetting the momentum of blood backflow that may occur in the catheter 2 and reducing the risk of blood backflow into the heparin flush solution storage cavity 5.

[0071] As a further embodiment provided by the present invention, spherical cavities are provided at the joints of the first acceleration channel 141, the second acceleration channel 142, and the third acceleration channel 143, and a negative pressure suction channel is communicated between adjacent two spherical cavities.

[0072] Specifically, the sudden change in the cross-section of adjacent acceleration channels will cause a sudden change in the fluid velocity, generating impact pressure. As a flexible transition space, the spherical cavity can accommodate part of the fluid to temporarily store energy, slow down the impact of the flow rate mutation on the system, and avoid damaging the catheter 2 due to pressure fluctuations. When the pressure in the sealing liquid storage cavity 5 is unstable, the spherical cavity can absorb the pressure fluctuations through volume changes. When the pressure surges, the spherical cavity temporarily stores the excess fluid to avoid channel overload. When the pressure drops, the temporarily stored fluid is released to maintain the continuity of liquid drainage. If the sealing liquid contains particles, the low-speed eddy current in the spherical cavity can promote the uniform distribution of the particles, prevent precipitation from blocking the narrow acceleration channels, and further improve the stability of the self-draining system.

[0073] As a further embodiment provided by the present invention, hydrophobic membranes are provided at both ports of the negative pressure suction channel, so that only gas can pass through the negative pressure suction channel.

[0074] Specifically, the sealing liquid is successively accelerated through the first acceleration channel 141, the second acceleration channel 142, and the third acceleration channel 143. The increase in the flow rate will cause the hydrostatic pressure of the fluid to decrease, thereby forming a negative pressure in the spherical cavity and the step-by-step suction of the negative pressure suction channel, so as to assist in maintaining a low-pressure environment in the liquid drainage channel 14, forming a pressure difference with the positive pressure in the sealing liquid storage cavity 5, further driving the flow of the sealing liquid, ensuring the continuity and stability of the liquid drainage process, and further improving the stability of the self-draining system.

[0075] As a further embodiment provided by the present invention, a first air passage is connected between the dynamic pressure balance cavity 8 and the catheter 2. A second air passage is connected between the first air passage near the air inlet port and the communication cavity 16, and a hydrophobic membrane is provided at the connection port of the second air passage and the communication cavity 16.

[0076] Specifically, during blood collection, since the catheter 2 is in a negative pressure state, the gas in the first chamber is sucked through the first air passage, thereby releasing part of the pressure in the catheter 2, keeping the negative pressure in the catheter 2 within the safe threshold range, effectively reducing the risk of blood vessel collapse during blood collection, thereby improving the safety during blood collection and reducing the incidence of medical accidents.

[0077] Furthermore, when the blood drawing is completed and the syringe needle is pulled out, the negative pressure in the catheter 2 is eliminated, and the pressure-sensitive piston 9 is driven to move in the opposite direction by the negative pressure difference, thereby driving the movable plate 12 to synchronously move in the opposite direction and reset in the movable groove 11, thereby driving the movable plate 12 to move to the side of the entrance of the liquid outlet channel 10 away from the connecting chamber 16, so that the liquid outlet channel 10 is connected with the connecting chamber 16 to open the first fluid passage, so that under the action of the residual negative pressure in the connecting chamber 16 and the pressure difference between the sealing liquid storage chamber 5, the sealing liquid is automatically released into the catheter 2 through the liquid outlet channel 10. When the movable plate 12 is reset, it scratches the entrance of the liquid outlet channel 10 to form a transient negative pressure. At the same time, the pressure-sensitive piston 9 sucks the connecting chamber 16 through the second air channel during the reverse movement, thereby further increasing the pressure difference between the sealing liquid storage chamber 5 and the connecting chamber 16, thereby further improving the stability of the self-draining system.

[0078] As a further embodiment of the present invention, an elastic membrane 15 is provided at the connection port between the first airway and the catheter 2 , a through hole is opened at the center of the elastic membrane 15 , and gaps are evenly distributed around the through hole to automatically adjust the size of the through hole according to the change of negative pressure in the catheter 2 .

[0079] Specifically, a groove connected to the first airway is provided on the side tube 6 of the catheter 2, and the elastic membrane 15 is provided in the groove. When blood is drawn, negative pressure is generated in the catheter 2, and the air pressure in the groove is greater than the negative pressure in the side tube 6, thereby forming a pressure difference on both sides of the elastic membrane 15. The elastic membrane 15 is sunken into the side tube 6 due to elasticity, and the gap around the central through hole is stretched open, and the effective cross-sectional area of the through hole is increased, allowing more gas to enter the catheter 2 through the first airway, quickly balancing the negative pressure and avoiding blood vessel collapse due to excessive negative pressure. The radial distribution of the gaps (similar to the petal structure) causes the membrane to deform in a stepped manner, and the through hole changes to:

[0080] When there is a slight negative pressure, only part of the gap is slightly opened, and the through hole is slightly enlarged to maintain low-flow air supply;

[0081] In severe negative pressure, when drawing blood, the full-circle gap is fully opened, the through hole is maximized, and emergency air replenishment is achieved, which can avoid the full opening or full closing sudden response of the traditional one-way valve and reduce the impact of pressure fluctuations on blood vessels;

[0082] The elastic membrane 15 closes quickly after the needle is removed, which can lock the residual negative pressure in the catheter 2 and cooperate with the negative pressure suction channel of the connecting cavity 16 to form a three-level negative pressure gradient, thereby enhancing the pressure difference between the sealing liquid storage cavity 5 and the catheter 2, driving the sealing liquid to fill the catheter cavity more thoroughly, and further improving the stability of the self-draining system.

[0083] As a further embodiment of the present invention, the liquid outlet channel 10 is arranged obliquely, and the liquid outlet port is lower than the liquid inlet port.

[0084] Specifically, the inclined arrangement of the liquid outlet channel 10 can make the drainage of the sealing liquid smoother.

[0085] As a further embodiment provided by the present invention, a filter screen is provided at the liquid inlet port of the liquid outlet channel 10.

[0086] Specifically, the filter screen provided can prevent the debris after the rupture of the balloon 7 from entering the catheter 2.

[0087] As a further embodiment provided by the present invention, a duckbill valve is provided in the main channel of the connector 1, and the opening faces the direction of the catheter 2.

[0088] Specifically, the duckbill valve provided forms a one-way flow channel to prevent blood backflow.

[0089] Only some exemplary embodiments of the present invention have been described by way of illustration above. Without doubt, for those of ordinary skill in the art, the described embodiments can be modified in various different ways without departing from the spirit and scope of the present invention. Therefore, the above drawings and descriptions are illustrative in nature and should not be construed as limiting the scope of protection of the claims of the present invention.

Claims

1. An arterial indwelling needle, characterized in that, include: Connectors and conduits provided for communication; A silicone plug, which is provided at the connection between the connector and the catheter; The tube sealing liquid storage chamber is provided inside the joint and is connected with the joint to form a first fluid passage; A pressure-responsive channel switching unit, comprising: A dynamic pressure balance chamber is disposed in the joint and is connected to the conduit to adjust the air pressure change in the dynamic pressure balance chamber in real time; A pressure sensitive piston is slidably disposed in the dynamic pressure balance chamber, and its displacement responds in real time to the change of the air pressure in the dynamic pressure balance chamber; A puncture assembly, comprising a moving plate and a puncture needle, wherein the moving plate is rigidly connected to the pressure-sensitive piston; A communication chamber, which is connected to the first fluid passage; a balloon disposed in the communication cavity and filling the communication cavity to block the first fluid passage; The pressure-responsive channel switching unit includes the following states: When the syringe is inserted into the silicone plug to draw blood, when the air pressure in the dynamic pressure balance chamber reaches a first threshold, the pressure sensitive piston moves to drive the moving plate to drive the puncture needle to puncture the balloon, and the first fluid passage is temporarily closed through the moving plate; After the syringe is pulled out, the negative pressure in the catheter is eliminated, and the pressure-sensitive piston moves in the opposite direction driven by the negative pressure difference in the dynamic pressure balance chamber, driving the movable plate to reset and open the first fluid passage, and automatically releases the sealing liquid into the catheter based on the pressure difference between the residual negative pressure in the connecting chamber and the sealing liquid storage chamber.

2. The arterial indwelling needle according to claim 1, wherein The first fluid passage includes a liquid outlet channel, a moving groove and a liquid discharge channel. The liquid outlet channel is connected between the moving groove and the main channel. The moving plate is slidably arranged in the moving groove. When the moving plate is reset, it scratches the entrance of the liquid outlet channel to form a transient negative pressure, thereby accelerating the sealing liquid to enter the catheter.

3. The arterial indwelling needle according to claim 2, wherein, The drainage channel is connected between the sealing liquid storage chamber and the connecting chamber, and includes a first acceleration channel, a second acceleration channel and a third acceleration channel which are connected in sequence, and the channel cross sections of the three decrease from the liquid inlet to the liquid outlet.

4. The arterial indwelling needle according to claim 3, wherein A spherical cavity is arranged at the connection of the first acceleration channel, the second acceleration channel and the third acceleration channel, and a negative pressure suction channel is arranged in communication between two adjacent spherical cavities.

5. The arterial indwelling needle according to claim 4, wherein, Hydrophobic membranes are arranged at the two ports of the negative pressure suction channel, so that only gas can pass through the negative pressure suction channel.

6. The arterial indwelling needle according to claim 5, characterized in that, A first airway is provided between the dynamic pressure balance chamber and the catheter, a second airway is provided between the first airway channel near the air inlet port and the communicating chamber, and a hydrophobic membrane is provided at the connecting port between the second airway and the communicating chamber.

7. The arterial indwelling needle according to claim 6, characterized in that, An elastic membrane is provided at the connection port between the first airway and the catheter, a through hole is provided at the center of the elastic membrane, and gaps are evenly distributed around the through hole to automatically adjust the size of the through hole according to the change of negative pressure in the catheter.

8. The arterial indwelling needle according to claim 7, characterized in that, The liquid outlet channel is arranged obliquely, and the liquid outlet port is lower than the liquid inlet port.

9. The arterial indwelling needle according to claim 8, wherein, A filter screen is arranged at the liquid inlet port of the liquid outlet channel.

10. The arterial indwelling needle according to claim 1, characterized in that, A duckbill valve is arranged in the main channel of the connector, and its opening faces the direction of the catheter.

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