Balloon counterpulsation device in double-balloon aorta

Abstract

The invention discloses a double-balloon in-aorta balloon counterpulsation device, and relates to the technical field of medical equipment. The balloon catheter comprises a control host, a catheter shaft, a main balloon and an auxiliary balloon, the catheter shaft is arranged on the control host, and the main balloon and the auxiliary balloon are arranged at the other end of the catheter shaft; the main balloon is a long-strip-shaped hollow air bag, the auxiliary balloon is any one of a cylindrical hollow air bag, a conical hollow air bag and a hemispherical hollow air bag, and an inner cavity of the main balloon is larger than an inner cavity of the auxiliary balloon. A guide wire channel is arranged in the catheter shaft and penetrates through the auxiliary balloon and the main balloon; by arranging the main balloon and the auxiliary balloon, when the left ventricle begins to contract and the aortic valve is opened, the main balloon begins to contract, and meanwhile, the auxiliary balloon delays to start to contract, so that the suction resistance to the telecentric end when the main balloon contracts is increased, the reverse blood flow extracted from the telecentric end is reduced, the suction effect on the proximal end is improved, and the cardiac output is increased.

Description

Technical Field

[0001] The invention relates to the technical field of medical equipment, in particular to a double-balloon intra-aortic balloon counterpulsation device. Background Art

[0002] When patients have severe heart failure, cardiac output is reduced and cannot maintain perfusion of important organs. At the same time, coronary artery perfusion is reduced. At this time, even if sufficient vasoactive drugs are given, it is still difficult to be effective. Intra-aortic balloon pump (IABP) is a method of inserting a balloon into the descending aorta. When the heart contracts and the aortic valve opens, the balloon is deflated quickly, creating a cavity effect to draw blood from the aorta, reducing the pressure in the aorta, thus reducing the left ventricular ejection resistance (left ventricular afterload), increasing cardiac output, and improving blood perfusion of important organs. When the heart begins to relax and the aortic valve closes, the balloon is inflated quickly to increase arterial diastolic pressure, thereby increasing coronary artery perfusion. Currently, IABP is one of the most commonly used mechanical circulatory assist devices for cardiogenic shock. The IABP in the prior art places a balloon (IAB balloon) connected to the IABP host in the aorta, and expands and contracts with the heartbeat under the control of the IABP host. At the beginning of cardiac contraction, the balloon deflates and contracts, reducing aortic pressure, thereby reducing left ventricular ejection resistance, decreasing myocardial oxygen consumption, and increasing cardiac output. During cardiac diastole, the balloon is inflated and expanded to increase blood supply to peripheral arteries, especially coronary arteries. However, when the IAB balloon contracts, it simultaneously draws blood from the aorta at both ends of the balloon, reducing the amount of blood drawn from the proximal end of the aorta and reducing the effect of assisting cardiac function. In view of the above problems, the inventor proposes a double-balloon intra-aortic balloon counterpulsation device to solve the above problems. Summary of the invention

[0003] In order to solve the above problems, the purpose of the present invention is to provide a double-balloon intra-aortic balloon counterpulsation device.

[0004] In order to solve the above technical problems, the present invention adopts the following technical solutions: a double-balloon intra-aortic balloon counterpulsation device, the counterpulsation device comprises a control host, a catheter shaft, a main balloon and an auxiliary balloon, the catheter shaft is arranged on the control host, and the main balloon and the auxiliary balloon are arranged at the other end of the catheter shaft; The main balloon is a long hollow balloon, the auxiliary balloon is a hollow balloon in any of cylindrical, conical and hemispherical shapes, and the inner cavity of the main balloon is larger than that of the auxiliary balloon; A guidewire channel is provided in the catheter shaft, and the guidewire channel passes through the auxiliary balloon and the main balloon; A first air channel and a second air channel are respectively arranged inside the catheter shaft. One end of the first air channel is connected to the inner cavity of the main balloon, and one end of the second air channel is connected to the inner cavity of the auxiliary balloon.

[0005] Preferably, a multi-way connector is provided between the control host and the catheter shaft, and the multi-way connector is a multi-airway connector, and the other ends of the first airway and the second airway are connected to the multi-way connector.

[0006] Preferably, a pressure measuring joint is provided at one end of the catheter shaft.

[0007] Preferably, a fixator is provided at one end of the catheter shaft.

[0008] Compared with the prior art, the present invention has the following beneficial effects: 1. In the present invention, by providing a main balloon and an auxiliary balloon, when the left ventricle begins to contract and the aortic valve opens, the main balloon begins to contract, and the auxiliary balloon starts to contract with a delay, so as to increase the resistance to suction to the distal end when the main balloon contracts, reduce the reverse blood flow drawn from the distal end, thereby increasing the suction effect on the proximal end, further reducing the afterload of the left ventricle, and thus increasing the cardiac output; 2. In the present invention, by providing a main balloon and an auxiliary balloon, when the left ventricle ends contraction, the auxiliary balloon and the main balloon end contraction simultaneously (or nearly simultaneously) to avoid blocking the forward blood flow to the distal end of the aorta. After the left ventricle ends contraction and the aortic valve closes, the main balloon and the auxiliary balloon begin to expand to supply blood to the aorta. During expansion, the main balloon and the auxiliary balloon can expand synchronously to supply blood to the aorta at both ends of the main balloon and the auxiliary balloon (consistent with traditional IABP); 3. In the present invention, according to actual needs, the auxiliary balloon can start the expansion process earlier than the main balloon, increase the distal resistance to increase the proximal aorta blood supply, and increase the blood supply to the coronary arteries, head and upper limbs. BRIEF DESCRIPTION OF THE DRAWINGS

[0009] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0010] Figure 1 The figure is a schematic diagram of the overall structure of a double-balloon intra-aortic balloon counterpulsation device of the present invention.

[0011] Figure 2 It is a schematic diagram of the partial structure of a double-balloon intra-aortic balloon counterpulsation device of the present invention.

[0012] Figure 3 This is a schematic diagram of the state of the counterpulsation device according to an embodiment of the present invention entering the aorta.

[0013] In the figure: 1. control host; 2. catheter shaft; 3. main balloon; 4. auxiliary balloon; 5. multi-way connector; 6. fixator; 7. pressure measuring connector; 21. guidewire channel; 22. first airway; 23. second airway. DETAILED DESCRIPTION

[0014] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0015] Example: Figure 1-3 As shown, the present invention provides a double-balloon intra-aortic balloon counterpulsation device, which includes a control host 1, a catheter shaft 2, a main balloon 3 and an auxiliary balloon 4. The control host 1 includes a driving system, a monitoring system, an adjusting system and a control system. The driving system, the monitoring system, the adjusting system and the control system control the inflation and deflation of the main balloon 3 and the auxiliary balloon 4, and can control the main balloon 3 and the auxiliary balloon 4 respectively to achieve their functions. This is the prior art and will not be described in detail here. The catheter shaft 2 is arranged on the control host 1, and the main balloon 3 and the auxiliary balloon 4 are arranged at the other end of the catheter shaft 2. The main balloon 3 is a long hollow airbag. The auxiliary balloon 4 is a hollow air balloon of any one of cylindrical, conical and hemispherical shapes. The inner cavity of the main balloon 3 is larger than the inner cavity of the auxiliary balloon 4. A guidewire channel 21 is arranged in the catheter shaft 2. The guidewire channel 21 passes through the auxiliary balloon 4 and the main balloon 3. By setting the guidewire channel 21, during the puncture operation, after the guidewire enters the interior of the aorta, the main balloon 3 and the auxiliary balloon 4 can be placed in the aorta through the guidewire channel 21. The interior of the catheter shaft 2 is respectively provided with a first airway 22 and a second airway 23. One end of the first airway 22 is connected to the inner cavity of the main balloon 3, and one end of the second airway 23 is connected to the inner cavity of the auxiliary balloon 4.

[0016] A multi-way connector 5 is provided between the control host 1 and the catheter shaft 2. The multi-way connector 5 is a multi-airway connector. The other ends of the first airway 22 and the second airway 23 are connected to the multi-way connector 5. A pressure measuring connector 7 is provided at one end of the catheter shaft 2. By providing the pressure measuring connector 7, the guidewire channel 21 can be connected to an external pressure measuring device through the pressure measuring connector 7 to measure the intra-arterial pressure. By providing the multi-way connector 5, the multi-way connector 5 is used to communicate with the first airway 22 and the second airway 23. When the counterpulsation pump in the control host 1 is operating, the counterpulsation pump can inject gas into the first airway 22 and the second airway 23 respectively through the multi-way connector 5. The injected gas can enter the main balloon 3 and the auxiliary balloon 4 respectively, so that the main balloon 3 and the auxiliary balloon 4 expand or contract. A fixer 6 is provided at one end of the catheter shaft 2. The fixer 6 is used to fix the catheter shaft 2. The fixer 6 is a butterfly-shaped piece fixed to the skin by sutures or glue.

[0017] The control host 1 controls the inflation, expansion, deflation and contraction of the main balloon 3 and the auxiliary balloon 4 by receiving the electrocardiogram signal or the arterial pressure signal; Specifically, when the left ventricle begins to contract and the aortic valve opens, the main balloon 3 begins to contract, and the auxiliary balloon 4 starts to contract with a delay, so as to increase the resistance to suction to the distal end when the main balloon 3 contracts, reduce the reverse blood flow drawn from the distal end, thereby increasing the suction effect on the proximal end, reducing the pressure at the proximal end of the aorta during heart contraction, reducing the afterload of the left ventricle, thereby increasing cardiac output and reducing myocardial oxygen consumption; At the end of left ventricular contraction, the auxiliary balloon 4 and the main balloon 3 end contraction simultaneously (or nearly simultaneously) to avoid blocking the forward blood flow to the distal end of the aorta; After the left ventricular contraction ends and the aortic valve closes, the main balloon 3 and the auxiliary balloon 4 begin to expand to supply blood to the aorta. During expansion, the main balloon 3 and the auxiliary balloon 4 may expand synchronously to supply blood to the aorta at both ends of the main balloon 3 and the auxiliary balloon 4 at the same time (consistent with the traditional IABP), or according to actual needs, the auxiliary balloon 4 may start the expansion process earlier than the main balloon 3 to increase the distal end resistance to increase the proximal end aortic blood supply, thereby increasing the blood supply to the coronary arteries, head and upper limbs; Working principle: Method 1: The control host 1 controls the inflation, expansion, deflation and contraction of the main balloon 3 and the auxiliary balloon 4 by receiving and collecting the patient's physiological signals; When the left ventricle begins to contract and the aortic valve opens, the main balloon 3 begins to contract, and the auxiliary balloon 4 starts to contract with a delay (delay time Δt) to increase the resistance to suction to the distal end when the main balloon 3 contracts and reduce the reverse blood flow drawn from the distal end, thereby increasing the suction effect on the proximal end and further reducing the left ventricular ejection resistance, thereby increasing cardiac output and reducing myocardial oxygen consumption; At the end of left ventricular contraction, the auxiliary balloon 4 and the main balloon 3 end contraction simultaneously (or nearly simultaneously) to avoid blocking the forward blood flow to the distal end of the aorta; After the left ventricular contraction ends and the aortic valve closes, the main balloon 3 and the auxiliary balloon 4 begin to expand to supply blood to the aorta; during expansion, the main balloon 3 and the auxiliary balloon 4 expand synchronously (synchronous start and synchronous end), and supply blood to the aorta at both ends of the main balloon 3 and the auxiliary balloon 4 at the same time (consistent with traditional IABP); Method 2: According to actual application requirements, during the expansion of the main balloon 3 and the auxiliary balloon 4, the auxiliary balloon 4 may be asynchronous with the main balloon 3 to achieve a specific treatment purpose; The details are as follows: the device structure, connection method, control principle of the main balloon 3 and the auxiliary balloon 4 are the same as those of the first embodiment, and the contraction process of the main balloon 3 and the auxiliary balloon 4 is the same as that of the first embodiment; During the expansion of the main balloon 3 and the auxiliary balloon 4, the auxiliary balloon 4 starts to expand at the same time or earlier than the main balloon 3, and completes the expansion process before the main balloon 3, so that the distal resistance of the main balloon 3 and the auxiliary balloon 4 increases, so as to increase the blood supply to the proximal aorta, that is, to increase the blood supply to the coronary artery, the head and the upper limbs; Method 3: During application, the time difference between the expansion and contraction of the main balloon 3 and the auxiliary balloon 4 can be dynamically adjusted to optimize the treatment effect; Taking the cases of method 1 and method 2 as an example, under the condition of real-time monitoring of the pressure in the aorta, by adjusting Δt, the pressure in the aorta is reduced or the area under the pressure-time curve is reduced during the contraction phase (left ventricular contraction phase) of the main balloon 3 and the auxiliary balloon 4; Or, under the guidance of other cardiac function and hemodynamic detection methods such as ultrasound, PiCCO, and floating catheter, the corresponding detection indicators can be optimized by adjusting Δt.

[0018] Obviously, those skilled in the art can make various changes and modifications to the present invention without departing from the spirit and scope of the present invention. Thus, if these modifications and variations of the present invention fall within the scope of the claims of the present invention and their equivalents, the present invention is also intended to include these modifications and variations.

Claims

1. A double-balloon intra-aortic balloon counterpulsation device, characterized in that: The counterpulsation device comprises a control host (1), a catheter shaft (2), a main balloon (3) and an auxiliary balloon (4); the catheter shaft (2) is arranged on the control host (1), and the main balloon (3) and the auxiliary balloon (4) are arranged at the other end of the catheter shaft (2); The main balloon (3) is a long hollow balloon, the auxiliary balloon (4) is a hollow balloon in any of a cylindrical, conical and hemispherical shape, and the inner cavity of the main balloon (3) is larger than the inner cavity of the auxiliary balloon (4); A guidewire channel (21) is provided in the catheter shaft (2), and the guidewire channel (21) passes through the auxiliary balloon (4) and the main balloon (3); A first air channel (22) and a second air channel (23) are respectively arranged inside the catheter shaft (2); one end of the first air channel (22) is connected to the inner cavity of the main balloon (3), and one end of the second air channel (23) is connected to the inner cavity of the auxiliary balloon (4).

2. A double-balloon intra-aortic balloon counterpulsation device as claimed in claim 1, characterized in that: A multi-way connector (5) is provided between the control host (1) and the catheter shaft (2); the multi-way connector (5) is a multi-airway connector; the other ends of the first airway (22) and the second airway (23) are connected to the multi-way connector (5).

3. A double-balloon intra-aortic balloon counterpulsation device as claimed in claim 1, characterized in that: One end of the catheter shaft (2) is provided with a pressure measuring joint (7).

4. A double-balloon intra-aortic balloon counterpulsation device as claimed in claim 1, characterized in that: One end of the catheter shaft (2) is provided with a fixer (6).

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