Ultrasonic thrombolysis device suitable for cardiovascular system

Abstract

The invention discloses a cardiovascular ultrasonic thrombolysis device and relates to the technical field of surgical instruments, the cardiovascular ultrasonic thrombolysis device comprises a puncture tube and a medicine injection assembly used for injecting thrombolysis medicine into a thrombolysis position, an ultrasonic assembly used for generating ultrasonic waves is arranged in the puncture tube, and the cardiovascular ultrasonic thrombolysis device further comprises a resistance reducing assembly used for reducing ultrasonic conduction acoustic resistance; the resistance reducing assembly comprises an air bag pipe movably connected to one end in the puncture pipe, a balloon is installed at one end of the outer circumferential face of the puncture pipe in an embedded mode, a catheter penetrating through the puncture pipe is fixedly connected between the air bag pipe and the balloon in an annular array mode, and an auxiliary branch pipe is fixedly connected to the other end of the outer circumferential face of the puncture pipe. The auxiliary branch tube penetrates into the puncture tube and is fixedly communicated with the air bag tube; the ultrasonic transmission loss is reduced by injecting the coupling agent, the thrombolysis efficiency is guaranteed, meanwhile, it is guaranteed that the thrombolysis speeds of all areas in the blood vessel are consistent as much as possible, and damage to the blood vessel caused by thrombolysis is reduced.

Description

Technical Field

[0001] The present invention relates to the technical field of surgical instruments, and in particular to a cardiovascular ultrasonic thrombolysis device. Background Art

[0002] Thrombosis is a type of cardiovascular disease that seriously endangers human health and life. When a thrombus forms in the body, plasminogen in the blood is partially enriched around the thrombus due to its considerable affinity for fibrin. Plasminogen activator can activate plasminogen into plasmin, and plasmin with serine protease activity can degrade fibrin that constitutes the thrombus skeleton, thereby playing a role in thrombolysis;

[0003] Ultrasonic thrombolysis is to focus ultrasonic waves in a small area, causing the temperature in this area to rise, resulting in coagulative necrosis. In thrombus dissolution, this coagulative necrosis effect can improve the thrombus dissolution rate. At the same time, ultrasonic waves can generate micro-vibrations in the thrombus structure, causing the fibrin network structure in the thrombus to loosen, increasing the effect of fibrinolytic enzymes on the thrombus. In addition, ultrasonic waves can also change the pressure and hydrodynamic characteristics of the blood vessel wall in the thrombus, increasing the contact between the thrombus surface and the thrombolytic agent;

[0004] However, in actual operation, ultrasonic waves often have a reduced propagation efficiency due to the influence of acoustic impedance. And during the thrombolysis process, as the thrombus dissolves, the ultrasonic generator will be eccentric in the blood vessel, which will cause different distances for the ultrasonic generator to emit sound waves to its surroundings, and then there will be deviations in the thrombus dissolution rates at different positions in the blood vessel, easily resulting in a phenomenon where the thrombus in some areas has been dissolved, while the thrombus in some other areas has not been dissolved, making the blood vessel wall in the areas where dissolution has been completed vulnerable to ultrasonic influence and damaged. Summary of the Invention

[0005] The purpose of the present invention is to propose a cardiovascular ultrasonic thrombolysis device to solve the problems of large ultrasonic transmission loss in traditional ultrasonic thrombolysis and different thrombus dissolution speeds in each area causing damage to blood vessels.

[0006] In order to achieve the above purpose, the present invention adopts the following technical scheme:

[0007] A cardiovascular ultrasonic thrombolysis device includes a puncture tube and a drug injection component for injecting thrombolytic drugs into the thrombolysis site. An ultrasonic component for generating ultrasonic waves is provided inside the puncture tube, and a resistance reduction component for reducing the acoustic impedance of ultrasonic wave conduction is further included;

[0008] The resistance reduction component includes an airbag tube movably connected to one end inside the puncture tube. One end of the outer circumferential surface of the puncture tube is embedded with a balloon. The airbag tube and the balloon are fixedly connected in an annular array with a catheter penetrating the puncture tube. The other end of the outer circumferential surface of the puncture tube is fixedly connected with an auxiliary agent branch pipe, and the auxiliary agent branch pipe penetrates to the inside of the puncture tube and is fixedly communicated with the airbag tube.

[0009] As a further description of the above technical solution:

[0010] The puncture tube is composed of an elastic part and a tough part. The elastic part is located between two balloons. The part of the puncture tube other than the elastic part is the tough part. The balloons and the inside of the airbag tube are used to fill the coupling agent.

[0011] As a further description of the above technical solution:

[0012] A gap is left between the outer circumferential surface of the airbag tube and the inner wall of the puncture tube.

[0013] As a further description of the above technical solution:

[0014] One end of the airbag tube close to the auxiliary agent branch pipe is provided with a cooling component. The cooling component includes a corrugated telescopic pipe fixedly connected to the airbag tube close to the auxiliary agent branch pipe. A pressure relief valve is movably connected to the connection part of the inside of the corrugated telescopic pipe and the airbag tube.

[0015] As a further description of the above technical solution:

[0016] The auxiliary agent branch pipe penetrates to the inside of the airbag tube and extends to its inner end.

[0017] As a further description of the above technical solution:

[0018] The medicine injection component includes a pipe joint at one end of the puncture tube away from the airbag tube. A medicine injection branch pipe is fixedly connected to the circumferential surface of the pipe joint. A medicine spraying hole is opened at one end of the circumferential surface of the puncture tube.

[0019] As a further description of the above technical solution:

[0020] The ultrasonic component includes a plugging tube movably inserted into the inside of the puncture tube. One end of the circumferential surface of the plugging tube is fixedly connected with ultrasonic generators in a linear array. The other end of the plugging tube is movably connected with a locking head, and the locking head is threadedly connected with the pipe joint.

[0021] As a further description of the above technical solution:

[0022] The diameter of the end of the plugging tube gradually decreases, and its end is a spherical surface.

[0023] In summary, due to the adoption of the above technical solutions, the beneficial effects of the present invention are as follows:

[0024] After the coupling agent is injected, it can promote the effective transfer of energy into the blood vessel wall. And the ultrasonic wave is converted into a pulsed sound pressure wave through the coupling agent inside the balloon catheter, which can safely pass through the soft tissue, reduce the thermal damage to the soft tissue, and the coupling agent reduces the acoustic impedance difference, ensuring the thrombolysis efficiency of the ultrasonic wave. In addition, with the continuous impact, part of the thrombus will be dissolved and discharged along with the blood, thereby improving the compliance of the blood vessel. When the thrombus is dissolved and discharged, the pressure on the balloon catheter will also decrease. And with the dissolution of the thrombus and the continuous injection of the coupling agent, at the same time, the balloon catheter corresponds to the elastic part of the puncture catheter, so that the balloon catheter will expand together with the elastic part of the puncture catheter, making the balloon catheter always fit against the inner side of the blood vessel, and then making the occlusion catheter located at the center of the blood vessel compared to the inside of the blood vessel. This minimizes the distance error when the ultrasonic generator emits sound waves to various regions of the blood vessel inner wall, so that the thrombi in various regions of the blood vessel can be dissolved as much as possible at the same time, reducing the possibility of damage to the blood vessel inner wall in the dissolved regions due to the dissolution of thrombi in some regions while the thrombi in other regions remain undissolved, and improving the safety of ultrasonic thrombolysis. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] Figure 1 Shows the overall structural schematic diagram provided according to an embodiment of the present invention;

[0026] Figure 2 Shows the partial structural schematic diagram of the resistance reduction component provided according to an embodiment of the present invention;

[0027] Figure 3 Shows the Figure 2 enlarged view at A in the present invention provided according to an embodiment of the present invention;

[0028] Figure 4 Shows the schematic diagram of the initial operation of the resistance reduction component provided according to an embodiment of the present invention;

[0029] Figure 5 Shows the schematic diagram of the resistance reduction component after running for a period of time provided according to an embodiment of the present invention;

[0030] Figure 6 Shows the structural schematic diagram of the cooling component provided according to an embodiment of the present invention;

[0031] Figure 7 Shows the partial structural schematic diagram of the ultrasonic component provided according to an embodiment of the present invention.

[0032] Legend Explanation:

[0033] 10. Puncture catheter;

[0034] 20. Medication injection assembly; 21. Pipe connector; 22. Medication spraying hole; 23. Medication injection branch pipe;

[0035] 30. Ultrasonic assembly; 31. Sealing pipe; 32. Locking head; 33. Ultrasonic generator;

[0036] 40. Resistance reduction assembly; 41. Airbag pipe; 42. Balloon; 43. Catheter; 44. Auxiliary agent branch pipe;

[0037] 50. Cooling assembly; 51. Corrugated expansion pipe; 52. Pressure relief valve. Detailed implementation manners

[0038] Next, the technical solutions in the embodiments of the present invention will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without making creative efforts belong to the scope of protection of the present invention.

[0039] As Figures 1-7 shown, the present invention provides:

[0040] A cardiovascular ultrasound thrombolysis device, including a puncture tube 10 and a medication injection assembly 20 for injecting thrombolytic drugs into the thrombolysis site. An ultrasonic assembly 30 for generating ultrasonic waves is provided inside the puncture tube 10, and a resistance reduction assembly 40 for reducing the acoustic resistance of ultrasonic wave conduction is further included;

[0041] The resistance reduction assembly 40 includes an airbag pipe 41 movably connected to one end inside the puncture tube 10. A balloon 42 is embedded and installed at one end of the outer circumferential surface of the puncture tube 10. A catheter 43 penetrating the puncture tube 10 is fixedly connected between the airbag pipe 41 and the balloon 42 in an annular array. An auxiliary agent branch pipe 44 is fixedly connected to the other end of the outer circumferential surface of the puncture tube 10, and the auxiliary agent branch pipe 44 penetrates into the puncture tube 10 and is fixedly communicated with the airbag pipe 41;

[0042] The medication injection assembly 20 includes a pipe connector 21 at the end of the puncture tube 10 away from the airbag pipe 41. A medication injection branch pipe 23 is fixedly connected to the circumferential surface of the pipe connector 21. A medication spraying hole 22 is opened at one end of the circumferential surface of the puncture tube 10;

[0043] The ultrasonic assembly 30 includes a sealing pipe 31 movably inserted into the puncture tube 10. Ultrasonic generators 33 are fixedly connected to one end of the circumferential surface of the sealing pipe 31 in a linear array. A locking head 32 is movably connected to the other end of the sealing pipe 31, and the locking head 32 is threadedly connected to the pipe connector 21; the diameter of the end of the sealing pipe 31 gradually decreases, and its end is a spherical surface.

[0044] The puncture tube 10 is composed of an elastic part and a ductile part. The elastic part is located between two balloons 42. The part of the puncture tube 10 except the elastic part is the ductile part. The balloons 42 and the inside of the balloon tube 41 are used to fill the coupling agent. There is a gap between the outer circumferential surface of the balloon tube 41 and the inner wall of the puncture tube 10 to ensure that the thrombolytic drug can be discharged from the medicine spraying holes 22 through the gap.

[0045] Specifically, first, puncture the patient's radial artery, then deliver the exchange guide wire through the radial artery to the thrombus position of the patient to complete the preliminary positioning. Then thread the puncture tube 10 onto the exchange guide wire and deliver the puncture tube 10 along the exchange guide wire to the thrombus position, while ensuring that the medicine spraying holes 22 on the puncture tube 10 and the balloon tube 41 cover the entire thrombus segment. Then withdraw the exchange guide wire, introduce the occlusion tube 31 into the inside of the puncture tube 10, and ensure that one end of the occlusion tube 31 extends out of the puncture tube 10 to block one end of the puncture tube 10. Then lock the occlusion tube 31 and the puncture tube 10 with the locking head 32 and the pipe joint 21. After that, inject the thrombolytic drug into the inside of the puncture tube 10 under high pressure through the medicine injection branch tube 23, so that the drug is evenly sprayed into the entire thrombus segment through the medicine spraying holes 22 widely distributed on the surface of the puncture tube 10, achieving the thrombolytic treatment effect. This step is repeated multiple times to dissolve all the thrombi.

[0046] Meanwhile, during the thrombolysis process, by connecting the occlusion tube 31 to the ultrasonic device, the ultrasonic generator 33 on the surface of the occlusion tube 31 emits ultrasonic waves. By focusing the ultrasonic waves in a smaller area, the temperature in this area rises, resulting in coagulative necrosis. In thrombus dissolution, this coagulative necrosis effect can improve the thrombus dissolution speed. At the same time, the ultrasonic waves can generate tiny vibrations in the thrombus structure, causing the fibrin network structure in the thrombus to loosen, increasing the effect of fibrinolysin on the thrombus. In addition, during the process of bubble formation and collapse generated by the ultrasonic waves in the liquid, strong local vibrations and pressure changes will occur, thereby changing the hydrodynamic characteristics inside the thrombus, increasing the contact between the thrombus surface and the thrombolytic agent, and promoting thrombus dissolution.

[0047] Based on this, during the thrombolysis process, coupling agent is also injected into the inside of the balloon tube 41 under high pressure through the auxiliary agent branch tube 44. After the coupling agent is injected, since the balloon tube 41 in the thrombus segment is compressed by the thrombus and cannot expand, the coupling agent inside the balloon tube 41 will enter the inside of the balloon 42, causing the balloons 42 at both ends of the balloon tube 41 to show the Figure 4 expansion phenomenon as shown in. After the coupling agent is injected, it can promote the effective transfer of energy into the blood vessel wall. And the ultrasonic waves are converted into pulsed sound pressure waves through the coupling agent inside the balloon tube 41, which can safely pass through the soft tissue, reduce the thermal damage to the soft tissue, and the coupling agent reduces the acoustic impedance difference, ensuring the thrombolytic efficiency of the ultrasonic waves.

[0048] In addition, as the impact continues, part of the thrombus will dissolve and be discharged with the blood, thereby improving the compliance of the blood vessel. When the thrombus dissolves and is discharged, the pressure exerted on the balloon tube 41 will also decrease. And as the thrombus dissolves and the coupling agent is continuously injected, at the same time, the balloon tube 41 corresponds to the elastic part of the puncture tube 10, causing the balloon tube 41 to Figure 4 shift Figure 5 towards, resulting in the balloon tube 41 always fitting against the inner side of the blood vessel, and thus making the occlusion tube 31 located at the center of the blood vessel interior relative to the blood vessel. When the ultrasonic generator 33 emits sound waves to various regions of the blood vessel inner wall, the distance error is minimized to the greatest extent. As a result, thrombi in various regions within the blood vessel are dissolved as much as possible at the same time, reducing the possibility of damage to the inner wall of the blood vessel in the already dissolved regions due to the dissolution of thrombi in some regions while other thrombi remain undissolved, and improving the safety of ultrasonic thrombolysis.

[0049] As Figure 3 shown Figure 6 in the figure, a cooling component 50 is provided at one end of the balloon tube 41 close to the auxiliary agent branch tube 44. The cooling component 50 includes a corrugated expansion tube 51 fixedly connected to the balloon tube 41 close to the auxiliary agent branch tube 44. A pressure relief valve 52 is movably connected to the connection part between the interior of the corrugated expansion tube 51 and the balloon tube 41; the auxiliary agent branch tube 44 penetrates into the interior of the balloon tube 41 and extends to its inner end.

[0050] Specifically, since ultrasonic waves generate high temperatures, after the temperature of the coupling agent rises, its effect will be unstable, thereby increasing the transmission loss of ultrasonic waves;

[0051] Based on this, by providing the corrugated expansion tube 51 and the pressure relief valve 52, since the coupling agent is continuously injected into the interior of the balloon tube 41, as the coupling agent in the interior of the balloon tube 41 increases, when the internal pressure reaches the threshold value of the pressure relief valve 52, part of the coupling agent will enter the interior of the corrugated expansion tube 51 through the pressure relief valve 52. And because the auxiliary agent branch tube 44 penetrates into the interior of the balloon tube 41 and extends to its inner end, the injection and outflow positions of the coupling agent are opposite to each other, enabling the coupling agent to circulate within the balloon tube 41. As a result, the coupling agent can enter the interior of the corrugated expansion tube 51 after the temperature rises, while the externally low-temperature coupling agent re-enters the interior of the balloon tube 41, ensuring that the coupling agent inside the balloon tube 41 is always in a stage with a relatively appropriate temperature, ensuring its stable reduction of the ultrasonic transmission loss. At the same time, as the coupling agent enters the interior of the corrugated expansion tube 51, the corrugated expansion tube 51 will expand, thereby increasing its internal volume and improving the storage of the coupling agent.

[0052] As described above, it is only the preferred specific embodiment of the present invention, but the protection scope of the present invention is not limited thereto. Any person skilled in the art within the technical scope disclosed by the present invention, according to the technical solution and inventive concept of the present invention, makes equivalent substitutions or changes, and should be covered within the protection scope of the present invention.

Claims

1. A cardiovascular ultrasonic thrombolysis device, comprising a puncture tube (10) and a drug injection component (20) for injecting a thrombolytic drug into a thrombolytic site, wherein an ultrasonic component (30) for generating ultrasonic waves is provided inside the puncture tube (10), characterized in that: Also included is a resistance reduction component (40) for reducing the acoustic resistance of ultrasonic wave conduction; The resistance reduction component (40) comprises an airbag tube (41) movably connected to one end of the interior of the puncture tube (10); a balloon (42) is embedded and installed at one end of the outer circumferential surface of the puncture tube (10); a catheter (43) penetrating the puncture tube (10) is fixedly connected between the airbag tube (41) and the balloon (42) in an annular array; an auxiliary agent branch tube (44) is fixedly connected to the other end of the outer circumferential surface of the puncture tube (10); and the auxiliary agent branch tube (44) penetrates the interior of the puncture tube (10) and is fixedly connected to the airbag tube (41).

2. The cardiovascular ultrasonic thrombolysis device according to claim 1, characterized in that: The puncture tube (10) is composed of an elastic part and a tough part, the elastic part is located between the two balloons (42), and the parts of the puncture tube (10) other than the elastic part are all tough parts, and the inside of the balloon (42) and the airbag tube (41) are used to fill coupling agent.

3. The cardiovascular ultrasonic thrombolysis device according to claim 1, characterized in that: A gap is left between the outer circumferential surface of the airbag tube (41) and the inner wall of the puncture tube (10).

4. The cardiovascular ultrasonic thrombolysis device according to claim 1, characterized in that: A cooling assembly (50) is provided at one end of the airbag tube (41) close to the auxiliary agent branch tube (44), and the cooling assembly (50) comprises a bellows telescopic tube (51) fixedly connected to the airbag tube (41) close to the auxiliary agent branch tube (44), and a pressure relief valve (52) is movably connected to the inside of the bellows telescopic tube (51) at the connection point with the airbag tube (41).

5. The cardiovascular ultrasonic thrombolysis device according to claim 1, characterized in that: The auxiliary agent branch pipe (44) penetrates into the interior of the airbag tube (41) and extends to the inner end thereof.

6. The cardiovascular ultrasonic thrombolysis device according to claim 1, characterized in that: The drug injection assembly (20) comprises a pipe joint (21) at one end of the puncture tube (10) away from the airbag tube (41), a drug injection branch pipe (23) is fixedly connected to the circumferential surface of the pipe joint (21), and a drug spraying hole (22) is opened at one end of the circumferential surface of the puncture tube (10).

7. The cardiovascular ultrasonic thrombolysis device according to claim 6, characterized in that: The ultrasonic assembly (30) comprises a blocking tube (31) movably inserted into the interior of the puncture tube (10); one end of the circumferential surface of the blocking tube (31) is fixedly connected to an ultrasonic generator (33) in a linear array; the other end of the blocking tube (31) is movably connected to a locking head (32), and the locking head (32) is threadedly connected to the pipe joint (21).

8. The cardiovascular ultrasonic thrombolysis device according to claim 7, characterized in that: The diameter of the end of the blocking tube (31) gradually decreases, and the end of the blocking tube (31) is spherical.

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