Ultrasound catheter for intracardiac monitoring

Abstract

The present invention discloses an ultrasonic catheter for intracardiac monitoring, comprising a monitoring catheter and an extravascular handheld portion, wherein a cavity pipeline is provided inside the monitoring catheter, the rear end of the cavity pipeline is connected to an airbag insufflation tube inside the main body of the extravascular handheld portion, and the front end of the cavity pipeline is connected to the airbag, an ultrasonic transducer and a pressure sensor are provided on the surface of the monitoring catheter, wherein the pressure sensor is close to the airbag, and a signal transmission interface is provided at the other end of the extravascular handheld portion; the present invention has a novel and compact structure, relatively low processing cost, and a simple method of use, can accurately measure intracardiac hemodynamic parameters such as continuous cardiac output, and can display two-dimensional ultrasonic images of the heart in real time, which is convenient for doctors to perform clinical treatment and use of medicines.

Description

Technical Field

[0001] The present application belongs to the field of intracardiac ultrasonic medical devices, and specifically relates to an ultrasonic catheter for intracardiac monitoring. Background Art

[0002] Clinically, the optimal treatment for patients with emergency chest pain and critical illnesses depends on accurate assessment of hemodynamic status. Hemodynamic monitoring is an indispensable tool during surgical anesthesia, intensive care unit (ICU), surgery, and emergency treatment. Obtaining hemodynamic-related parameters through invasive or non-invasive methods reveals physiological or pathological changes in the body, thereby providing a comprehensive and in-depth understanding of the patient's condition and progression, facilitating diagnosis and prognosis. The application of hemodynamic-related science has played a vital role in determining clinical treatment direction, selecting treatment methods, and controlling the severity of the disease, and can guide clinicians' treatment and medication.

[0003] Currently, there are three commonly used methods for monitoring cardiac hemodynamics in clinical practice: transesophageal ultrasound, thermodilution, and intravascular ultrasound imaging (IVUS).

[0004] Transesophageal ultrasound involves a simple structure, primarily using a thin catheter passed through the esophagus. The ultrasound probe at its tip is positioned just behind the heart through the esophagus. Its advantages include avoiding the interference of the chest wall, ribs, and air in the lungs, which is common with transthoracic echocardiography, while also producing exceptionally clear echocardiographic images, free of external interference and other tissue artifacts, facilitating accurate diagnosis. However, its disadvantages include: ① The need for insertion into the human body causes considerable discomfort and complications after the patient recovers from anesthesia. This examination is not suitable for patients with esophageal or gastric ulcers, or for patients with severe arrhythmias, which can be precipitated by transesophageal ultrasound. ② Transesophageal ultrasound can only monitor hemodynamics while the patient is anesthetized; continuous monitoring is not possible after the patient awakens, and clinical conditions are quite restrictive. ③ Transesophageal ultrasound has a limited observation range, reaching only 4 cm from the center of the instrument's main shaft. ④ Esophageal ultrasound requires manual search for cardiac monitoring sites in the esophagus or stomach. The training period for learning this technology is at least 6 months. It cannot continuously monitor cardiac output in real time, and some parts require manual calculation.

[0005] Thermodilution involves inserting a floating catheter transvenously into the venous system, passing through the right atrium and right ventricle to the pulmonary artery. This allows for continuous measurement of pulmonary artery pressure during anesthesia. Furthermore, the balloon at the distal end of the catheter is inflated, allowing it to float with the blood flow and wedge into the distal pulmonary arterioles, thereby blocking blood flow and measuring pulmonary capillary wedge pressure. Currently, conventional floating catheters can measure a variety of hemodynamic parameters: pulmonary artery pressure (PAP), pulmonary capillary wedge pressure (PWP), right atrial pressure (RAP), cardiac output (CO), pulmonary vascular resistance (PVR), systemic vascular resistance (SVR), stroke work (SW), left ventricular stroke work (LVSW), right ventricular stroke work (RVSW), and cardiac index (CI). If necessary, a mixed venous blood sample can be obtained through the catheter to measure venous oxygen partial pressure (PvO), indirectly assessing pulmonary ventilation function. However, while monitoring the above functions, it also requires the following external devices to assist the device in completing the corresponding data monitoring, such as pressurized infusion bags, physiological monitors, pressure transducers, flushing devices, additional infusion pendants and interfaces, central venous interfaces, air bag openings, distal openings, thermistor connection ports, cardiac output measurement interfaces, catheter sheath infusion bypass interfaces, catheter sheath infusions and pendants, etc.

[0006] IVUS is used in the cardiac catheterization laboratory and is mainly inserted into the coronary arteries of the heart. By analyzing the IVUS images, the distribution range, severity and composition of coronary atherosclerotic lesions of the heart are evaluated; the location of coronary stent implantation and the effect of the operation are evaluated. The catheter is immediately withdrawn after the operation and continuous measurement cannot be achieved.

[0007] In summary, we need a novel and compact device in clinical practice that can measure hemodynamic parameters such as continuous cardiac output (CCO) and display real-time two-dimensional cardiac ultrasound images in the non-operative period. Summary of the Invention

[0008] To solve the above problems, the present invention discloses an ultrasonic catheter for intracardiac monitoring, which has a novel and compact structure, is easy to use, can accurately measure parameters such as continuous cardiac output, and display two-dimensional ultrasonic images of the heart in real time, facilitating doctors' clinical treatment and medication.

[0009] To achieve the above object, the technical solution of the present invention is as follows:

[0010] An ultrasonic catheter for intracardiac monitoring comprises a monitoring catheter and an extravascular handheld portion, and is characterized in that a cavity pipeline is provided inside the monitoring catheter, the rear end of the cavity pipeline is connected to the airbag insufflation tube inside the main body of the extravascular handheld portion, and the front end of the cavity pipeline is connected to the airbag, and a signal transmission interface is provided at the other end of the extravascular handheld portion; a pressure sensor is also provided on the surface of the monitoring catheter, and the pressure sensor is arranged close to the airbag; an ultrasonic transducer is also provided on the surface of the monitoring catheter, and the ultrasonic transducer is 280-400 mm away from the airbag.

[0011] Furthermore, the monitoring catheter has a length of 900-1100 mm and a diameter of 2.3-2.7 mm, and is made of high-density polyethylene.

[0012] Furthermore, the pressure sensor is 3-5 mm away from the airbag. The pressure sensor is a universal pressure sensor. When the airbag is inflated, the pressure sensor can effectively measure 360° intravascular pressure in the blood vessel within this distance, avoiding interference during airbag inflation.

[0013] Furthermore, the ultrasonic catheter also includes an ultrasonic probe, which includes a main body packaging tube, an ultrasonic transducer, a quartz reflector, and a micro gas turbine. The ultrasonic transducer and the micro gas turbine are respectively arranged on both sides of the main body packaging tube, and the power supply line of the ultrasonic transducer is arranged along the wall of the main body packaging tube. The rear end of the micro gas turbine is provided with an air inlet pipe and an air outlet pipe. The quartz reflector is arranged on the output shaft of the micro gas turbine, and the surface of the quartz reflector is provided with at least one reflecting surface.

[0014] Furthermore, the main body packaging tube has a diameter of 2.3-2.9 mm and a length of 3.5-4 mm, and is made of polycarbonate.

[0015] Furthermore, the ultrasonic transducer is a phased array micro transducer with a diameter of 1 mm, a 64*1, 64*2 or 64*3 crystal phased array, and is led out by 64 coaxial cables and connected to the external host.

[0016] Furthermore, the quartz reflector is a circular wedge with a diameter of 1 mm and a section at an angle of 45°, and the center of the bottom of the quartz reflector is fixed on the output shaft of the micro turbine.

[0017] The present invention also discloses a multi-balloon ultrasonic catheter for intracardiac monitoring, comprising a monitoring catheter and an extravascular handheld part, and is characterized in that: the monitoring catheter is provided with a floating guide balloon, a PAOP pressure transducer, an occlusion pressure balloon, a Cvp pressure transducer, and an ultrasonic transducer in sequence from the top of the catheter; a cavity pipeline is provided inside the monitoring catheter, and the cavity pipeline is respectively connected to the occlusion pressure balloon injection port and the floating guide balloon injection port on the extravascular handheld part; the cavity pipeline connects the occlusion pressure balloon and the floating guide balloon at the front end of the catheter, and the ultrasonic transducer is 280-400 mm away from the top of the catheter.

[0018] Furthermore, the monitoring catheter has a temperature sensor at the front end; an occlusion pressure airbag, which is 70-100 mm away from the top of the catheter; a PAOP pressure transducer, which has a diameter of 2.3-3 mm and is 50-70 mm away from the top of the catheter; a floating guide airbag, which is 20-40 mm away from the top of the catheter; and a Cvp pressure transducer, which is set close to the ultrasonic transducer.

[0019] The beneficial effects of the present invention are:

[0020] (1) An ultrasonic catheter for intracardiac monitoring, which has a novel and compact structure and is easy to use. It can accurately measure parameters such as continuous cardiac output and display two-dimensional ultrasonic images of the heart in real time, making it easier for doctors to perform clinical treatment and administer medication.

[0021] (2) The ultrasonic transducer is set close to the airbag. At this time, the ultrasonic transducer is located at the pulmonary valve of the right ventricle, which is the center of the entire heart cavity (an unconventional position). At this position, the ultrasonic transducer can use the minimum ultrasonic energy to display the most complete heart cavity structure, and can more accurately measure the output of the pulmonary artery.

[0022] (3) Compared with esophageal ultrasound, its advantages are as follows:

[0023] Real-time observation to accurately understand the morphological characteristics of the heart chambers and pulmonary artery vascular walls;

[0024] Because the intracardiac ultrasound monitoring catheter is placed inside the vascular cavity, ultrasound imaging can quickly observe the pulmonary artery and its branches over a wider range, diagnose pulmonary embolism, and guide clinicians in rapid treatment and removal of thrombi.

[0025] Awake patients cannot tolerate transesophageal ultrasound monitoring, while the "intracardiac ultrasound monitoring catheter" is suitable for all critically ill patients and anesthetized patients;

[0026] Esophageal ultrasound requires manual search for cardiac monitoring sites in the esophagus or stomach. The training period for learning this technology is at least 6 months. It cannot continuously monitor cardiac output in real time, and some calculations require manual calculation. However, the "intracardiac ultrasound monitoring catheter" can continuously and real-time display the blood flow Doppler waveform and measure the stroke volume and cardiac output per minute.

[0027] (4) Compared with the thermodilution method, the advantages are as follows:

[0028] To evaluate the imaging structure and function of the whole heart, the Doppler waveform of blood flow in the right ventricular outflow tract (RVOT) or main pulmonary artery (MPA) can be displayed and measured in real time, and the stroke volume and cardiac output per minute can be measured.

[0029] No additional testing consumables are required, which reduces costs; at the same time, the monitoring indicators are richer, and the data monitored by the pressure transducer and ultrasonic transducer are functional data.

[0030] (5) Advantages over IVUS are as follows:

[0031] It is inserted into the right ventricular system of the heart (right atrium, right ventricle and pulmonary artery), can be left in the heart cavity for a short or long term, has hemodynamic monitoring function, and is suitable for various critically ill patients. It can be widely used in the operating room anesthesia department, intensive care unit (ICU), cardiology CCU, respiratory department and other critically ill patients for continuous hemodynamic monitoring and guidance of clinicians to judge the condition based on monitoring indicators, and conduct individualized diagnosis and treatment medication.

[0032] (6) Multi-balloon ultrasound catheter can realize the measurement of multiple parameters, with simple structure and easy operation. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the specific implementation methods of the present application or the technical solutions in the prior art, the following is a brief introduction to the drawings required for use in the specific implementation methods or the description of the prior art. Obviously, the drawings described below are some implementation methods of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0034] Figure 1 This is a schematic diagram of the monitoring catheter structure of the present invention.

[0035] Figure 2 This is a schematic structural diagram of the extravascular handheld portion of the present invention.

[0036] Figure 3 This is a usage state diagram of the present invention.

[0037] Figure 4 It is a schematic diagram of the structure of the multi-balloon ultrasonic catheter of the present invention.

[0038] Figure 5 Schematic diagram of the ultrasonic probe structure of the present invention.

[0039] List of Figure Symbols:

[0040] 1. Monitoring catheter, 2. Ultrasonic transducer, 3. Pressure sensor, 4. Airbag, 5. Scale, 6. Main body of the handheld part outside the blood vessel, 7. Handheld device, 8. Signal transmission interface, 9. Airbag insufflation tube, 10. Cavity pipeline, 11. Control valve, 12. Pulmonary artery terminal.

[0041] 3', Cvp pressure transducer, 3", PAOP pressure transducer, 4', occlusion pressure airbag, 4", floating guide airbag, 13, temperature sensor, 14, SPO2 optical fiber.

[0042] 21. Main packaging tube, 22. Ultrasonic energy generator, 23. Quartz reflector, 24. Micro gas turbine, 25. Inlet pipe, 26. Outlet pipe. DETAILED DESCRIPTION

[0043] The following will clearly and completely describe the technical solutions of this application in conjunction with the embodiments. Obviously, the embodiments described are only part of the embodiments of this application, not all of them. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0044] Example 1

[0045] As shown in the figure, the ultrasonic catheter for intracardiac monitoring described in the present invention includes two parts: a monitoring catheter 1 and an extravascular handheld part body 6. A cavity pipeline is provided inside the monitoring catheter 1. The rear end of the cavity pipeline is connected to the airbag insufflation tube inside the extravascular handheld part body 6, and the front end of the cavity pipeline is connected to the airbag 4. An ultrasonic transducer 2 and a pressure sensor 3 are provided on the surface of the monitoring catheter 1, wherein the pressure sensor 3 is close to the airbag 4. A signal transmission interface is provided at the other end of the extravascular handheld part body 6.

[0046] The monitoring catheter 1 is as follows Figure 1 As shown, the overall length is 1000mm, the diameter is 2.5mm, and the tube material is high-density polyethylene; the ultrasonic transducer 2 is set on the surface of the monitoring catheter and is bonded 320mm away from the top by adhesive; the pressure sensor 3 is set on the surface of the monitoring catheter and must be placed in the aorta when in use. It is bonded by adhesive and is 4mm away from the top of the monitoring catheter 1, which can display the pressure value at the end of the aorta.

[0047] The inflatable balloon 4 is arranged at the top of the monitoring catheter 1, and can pass CO2 gas through the monitoring catheter 1 during the implantation process. Figure 1 The built-in cavity pipeline 10 in the middle dotted line is injected into the airbag 4. The diameter of the airbag is 2.3 mm in the uninflated state. After inflation, the diameter is 10-13 mm and the volume is 1.2-1.5 ml.

[0048] At the end of the monitoring catheter 1, Figure 1 The scale 5 shown in the figure is used to display the length of the monitoring catheter 1 entering the human blood vessel, so as to roughly judge whether it is in place.

[0049] The extravascular handheld part includes a main body 6 of the handheld part, a handpiece 7, a signal transmission interface 8, and a balloon insufflation tube 9.

[0050] The top of the main body 6 of the handheld part is connected to the end of the monitoring catheter 1. Most of the balloon insufflation tube 9 is located inside the main body 6 of the handheld part. One end is connected to the cavity pipeline 10 for injecting medical CO2 gas, so that the catheter reaches the aorta with the blood flow in the heart cavity, and can release the gas after it is in place; the other end extends out of the main body 6 of the handheld part, and the end is provided with a control valve 11 for controlling the intake or deflation.

[0051] Figure 2 The handheld device 7 includes two symmetrically arranged rings with a diameter of 24 mm. During the operation, the doctor's index finger and middle finger can be embedded in the rings to facilitate the adjustment and fixation of the angle and depth of the catheter in the heart cavity.

[0052] Figure 2 The middle signal transmission interface 8 is made of a round copper electromagnetic wire wrapped with polyurethane nylon thread. It connects the ultrasonic transducer 2 and the pressure sensor 3 and can transmit intracardiac ultrasonic signals and intra-aortic pressure signals to external devices.

[0053] The ultrasonic transducer 2 is a phased array micro transducer with a diameter of 1 mm and a 64*2 crystal array phased array. It is led out by 64 coaxial cables and connected to the external host.

[0054] Compared with traditional transesophageal ultrasound, thermodilution and IVUS methods, intracardiac ultrasound using the ultrasound catheter of the present invention has the following advantages and differences:

[0055]

[0056]

[0057] Example 2

[0058] Based on Example 1, the monitoring catheter 1 has an overall length of 900 mm and a diameter of 2.3 mm, and the ultrasonic transducer 2 is 280 mm away from the top end;

[0059] The pressure sensor 3 is 3 mm away from the top of the monitoring catheter 1. The handheld device 7 includes two symmetrically arranged circular rings with a diameter of 22 mm. The ultrasonic transducer 2 is a 64*1 crystal phased array.

[0060] Example 3

[0061] Based on Example 1, the monitoring catheter 1 has an overall length of 1100 mm and a diameter of 2.7 mm, and the ultrasonic transducer 2 is 360 mm away from the top end;

[0062] The pressure sensor 3 is 5 mm away from the top of the monitoring catheter 1. The handheld device 7 includes two symmetrically arranged circular rings with a diameter of 26 mm. The ultrasonic transducer 2 is a 64*3 crystal phased array.

[0063] Example 4

[0064] Figure 4 This is a schematic diagram of the improved multi-balloon ultrasound catheter structure of the present invention. The monitoring catheter 1 is 110 cm long, made of high-density polyethylene, and has a diameter of 3 mm. The ultrasonic transducer 2 is located 400 mm from the catheter's tip. The occlusion pressure balloon 4' is located 100 mm from the catheter's tip. Its diameter in the uninflated state is 2.3-3 mm, and when inflated, it has a diameter of 1.3-1.5 mm, with a volume of 1.5-1.8 ml. The PAOP pressure transducer 3" is 3 mm in diameter and located 70 mm from the catheter's tip. The floating guide balloon 4" is located 40 mm from the catheter's tip. Its diameter in the uninflated state is 2.3-3 mm, and when inflated, it has a diameter of 10-12 mm, with a volume of 1.3-1.5 ml. The oxygen saturation (SPO2) sensor transmission fiber 14 is placed throughout the catheter lumen. The temperature sensor 13 is located at the catheter's tip. A scale 5 indicates the catheter's depth within the body. The CVP pressure transducer 3' is located close to the ultrasonic transducer.

[0065] During operation, (1) the patient lies quietly and the needle is inserted from the subclavian vein close to the apex of the lung; (2) the monitoring catheter is implanted into the human body from step (1), and the pressure waveform is constantly observed through the signal transmitted by the PAOP pressure transducer 3" on the catheter, while the catheter is slowly inserted. When the scale 5 on the catheter shows a depth of about 15-20 cm, CO2 gas is injected into the airbag through the syringe on the handheld end, so that it floats into the heart cavity along the blood flow. At this time, the ultrasonic transducer 2 transmits the signal to the external device, and the doctor can see the waveforms of the right atrium, right ventricle, pulmonary artery and the ultrasonic two-dimensional image on the screen in turn; (3) the pressure on the catheter is observed. The doctor then looks at the ultrasound 2D image and pressure waveform displayed on the screen and advances the catheter another 38-50cm to determine that the catheter tip is placed in the pulmonary artery. At this point, the ultrasound transducer 2 and Cvp pressure transducer 3' are located at the entrance of the left ventricle aortic valve, and the occlusion pressure balloon 4', PAOP pressure transducer 3", floating guide balloon 4", and temperature sensor 13 are located in the aorta. The gas in the floating guide balloon 4" is then released. The signal transmitted by the PAOP pressure transducer 3" is displayed on an external device as the measured pulmonary artery pressure (PAP). At this point, 1.2-1.5ml CO2 gas is injected into the floating guide balloon 4" through the floating guide balloon injection port of the monitoring catheter 1. The balloon has a diameter of 2.3-3mm in the uninflated state and a diameter of 10-12mm after inflation, with a volume of 1.3-1.5ml. At this time, the PAOP pressure transducer 3" is located in the aorta, and the pressure value measured is the aortic pressure. At this time, the PPAOP pressure transducer 3" at the front end of the catheter can display a regular pressure waveform. (4) Based on the regular pressure waveform transmitted by the PAOP pressure transducer 3" and the two-dimensional ultrasound image of the cardiac cavity transmitted by the ultrasound transducer 2 at this time, the doctor releases the gas in the balloon and fine-tunes the position of the ultrasound transducer 2. Based on the two-dimensional ultrasound image and pressure waveform, the doctor can determine that the ultrasound transducer 2 is at the entrance of the pulmonary artery. At this time, the distance between the ultrasound transducer 2 and the top is 400mm. (5) CO2 gas is injected into the occlusion pressure balloon 4' through the Cvp occlusion pressure balloon injection port of the monitoring catheter; the balloon has a diameter of 2.3-3mm in the uninflated state and a diameter of 1.3-1.5mm after inflation, with a volume of 1.5-1.8ml; the pressure measured at this time is the Cvp pulmonary artery occlusion pressure. (6) The monitoring catheter 1 is fixed, and the intracardiac ultrasound signal and the intra-aortic pressure signal are continuously transmitted to the peripheral device.

[0066] Example 5

[0067] Based on Example 4, the monitoring catheter 1 is 90 cm long, made of high-density polyethylene, and has a diameter of 2.3 mm; the ultrasonic transducer 2 is located 280 mm from the top of the catheter; the occlusion pressure balloon 4' is 70 mm from the top of the catheter; the PAOP pressure transducer 3" has a diameter of 2.3 mm and is 50 mm from the top of the catheter; and the floating guide balloon 4" is 20 mm from the top of the catheter.

[0068] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present application, rather than to limit them. Although the present application has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some or all of the technical features therein. These modifications or replacements do not deviate the essence of the corresponding technical solutions from the scope of the technical solutions of the embodiments of the present application.

Claims

1. An ultrasonic catheter for continuous intracardiac monitoring, comprising a monitoring catheter and an extravascular handheld portion, characterized in that: The monitoring catheter is provided with a cavity tube inside, the rear end of which is connected to the airbag insufflation tube inside the main body of the handheld portion outside the blood vessel, and the front end of the cavity tube is connected to the airbag. The other end of the handheld portion outside the blood vessel is provided with a signal transmission interface. The monitoring catheter is also provided with a pressure sensor and an ultrasonic transducer on the surface of the monitoring catheter. The pressure sensor is arranged near the airbag, 3-5 mm away from the airbag. The ultrasonic transducer is 280-400 mm away from the top of the catheter and is placed at the pulmonary valve of the right ventricle during monitoring. It uses minimal ultrasonic energy to display the most complete cardiac cavity structure, and is used to display real-time two-dimensional ultrasonic images of the heart and calculate pulmonary artery output. It also includes an ultrasonic probe, which includes a main body packaging tube, an ultrasonic energy generator, a quartz reflector, and a micro gas turbine. The ultrasonic energy generator and the micro gas turbine are respectively arranged on both sides of the main body packaging tube. The power supply line of the ultrasonic energy generator is arranged along the wall of the main body packaging tube. The rear end of the micro gas turbine is provided with an air inlet pipe and an air outlet pipe. The quartz reflector is arranged on the output shaft of the micro gas turbine, and the surface of the quartz reflector is provided with at least one reflecting surface.

2. The ultrasonic catheter for continuous intracardiac monitoring according to claim 1, characterized in that: The monitoring catheter has a length of 900-1100 mm and a diameter of 2.3-2.7 mm, and is made of high-density polyethylene.

3. The ultrasonic catheter for continuous intracardiac monitoring according to claim 1, characterized in that: A handpiece is provided in the middle of the extravascular handheld part. The handpiece is two circular rings with a diameter of 24±2 mm. The two circular rings are symmetrically arranged around the main body of the extravascular handheld part.

4. The ultrasonic catheter for continuous intracardiac monitoring according to claim 1, characterized in that: A scale is provided on the rear end surface of the monitoring catheter.

5. The ultrasonic catheter for continuous intracardiac monitoring according to claim 1, characterized in that: A control valve is provided at the front end of the air bag inflating tube.

6. The ultrasonic catheter for continuous intracardiac monitoring according to claim 1, characterized in that: The ultrasonic transducer is a phased array micro transducer with a diameter of 1 mm and a 64*1, 64*2 or 64*3 crystal phased array. It is led out by 64 coaxial cables and connected to the external host.

7. A multi-balloon ultrasound catheter for continuous intracardiac monitoring, comprising a monitoring catheter and an extravascular handheld portion, characterized in that: The monitoring catheter is provided with a floating guide airbag, a PAOP pressure transducer, an occlusion pressure airbag, a CVP pressure transducer, and an ultrasonic transducer in order from the top of the catheter; a cavity pipeline is provided inside the monitoring catheter, and the cavity pipeline is respectively connected to the occlusion pressure airbag injection port and the floating guide airbag injection port on the manual control part outside the blood vessel. The cavity pipeline connects the occlusion pressure airbag and the floating guide airbag at the front end of the catheter; in, The floating guide balloon is 20-40 mm away from the top of the catheter and has a diameter of 10-12 mm after inflation; The PAOP pressure transducer is 50-70 mm away from the top of the catheter and has a diameter of 2.3-3 mm; The occlusion pressure balloon is 70-100 mm away from the top of the catheter; The Cvp pressure transducer is arranged close to the ultrasonic transducer; The ultrasonic transducer is 280-400 mm away from the top of the catheter and is placed at the pulmonary valve of the right ventricle during monitoring. It uses minimal ultrasonic energy to display the most complete cardiac cavity structure, and is used to display real-time two-dimensional ultrasonic images of the heart and calculate pulmonary artery output. A temperature sensor is also provided at the front end of the catheter.

8. The multi-balloon ultrasound catheter for continuous intracardiac monitoring according to claim 7, characterized in that: The monitoring catheter has a length of 900-1100 mm and a diameter of 2.3-3 mm, and is made of high-density polyethylene.

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