CN210811480U - Mapping electrode catheter capable of evaluating pulmonary vein occlusion condition - Google Patents

Abstract

The application provides a mapping electrode catheter capable of evaluating pulmonary vein occlusion conditions, comprising: the device comprises an ablation plugging device, a sheath tube, an electric signal detection catheter and a plugging detection processor; the ablation occluder is an expansion occluder which expands during inflation or under the control of a signal, and is provided with an internal guide wire cavity; one end of the ablation plugging device is pushed out from the sheath tube, and the other end of the ablation plugging device is provided with an internal guide wire cavity outlet; the sheath tube is a catheter with a hollow inner cavity, and the proximal part of the sheath tube is connected with the ablation occluder; the proximal part of the electric signal detection catheter penetrates out of the outlet of the internal wire guide cavity, the distal part of the electric signal detection catheter is a bent electrode catheter, and a mapping electrode and an image collector are arranged in the inner cavity of the bent electrode catheter; and the plugging detection processor is connected with the image collector, receives the collected image of the image collector, displays the image after processing according to a preset processing strategy. The utility model discloses can be fast, safe harmless, accurately and the low-cost pulmonary vein shutoff condition of acquireing.

Description

Mapping electrode catheter capable of evaluating pulmonary vein occlusion condition

Technical Field

The application relates to the technical field of pulmonary vein occlusion condition judgment, in particular to a mapping electrode catheter capable of evaluating a pulmonary vein occlusion condition.

Background

Studies have shown that the vast majority of the sources of atrial fibrillation are from the pulmonary veins (four of which communicate with the left atrium). The heart is divided into a left atrium and a right atrium and a left ventricle and a right ventricle, a sinus node positioned at the upper part of the right atrium regularly sends pulse instructions, and after the electrical signals are temporarily delayed at the atrioventricular node, the electrical signals reach the whole heart through a conduction system, so that the heart generates synchronous and coordinated contraction. The heart beats once every impulse in the sinoatrial node, which is called "sinus rhythm" in medicine, and is a normal heart rhythm of the human body, and the frequency is 60-100 times per minute.

However, the normal electrical conduction system in the heart may be disturbed by irregular electrical signals from outside the sinoatrial node, resulting in tachycardia, irregular beating and further development of arrhythmia. One of the most common arrhythmia is atrial fibrillation, when the arrhythmia occurs, the atrium of a patient can rapidly and irregularly vibrate, the risk of stroke caused by atrial fibrillation is increased by five times, the death rate is increased by two times, the risk of heart failure is also increased by three times, and the health of the patient is greatly influenced.

Currently, there are two main therapeutic methods for atrial fibrillation, namely drug therapy and catheter ablation therapy. According to the difference of energy sources, the catheter ablation treatment is divided into various ways such as radio frequency catheter ablation, freezing balloon ablation, laser balloon ablation, ultrasonic ablation and the like, and the former two ways are mature at present. The main principle of catheter ablation is to destroy the tissue at the interface between the left atrium and each pulmonary vein, so that the tissue permanently loses the ability to conduct electricity, and further to isolate the interference of electrical signals from the pulmonary veins, so that the interference signals cannot pass through the ablated tissue and further cannot be transmitted into the heart, and the electrical conduction system of the heart is recovered to be normal.

The traditional radiofrequency catheter ablation is single-point ablation, the ablation needs to be carried out at the interface of the pulmonary vein and the left atrium point by point, and finally all ablation points form a ring shape to isolate all electric signal interference from the pulmonary vein. The freezing saccule is used for sealing the pulmonary vein opening, then cold fluid is sprayed into the saccule, tissues of the whole pulmonary vein opening are damaged at one time in a low-temperature mode, and compared with single-point radio frequency ablation, the ablation efficiency of the freezing saccule has great advantages. Cryoablation surgical instruments for accessing the left atrium generally include: an adjustable bending sheath tube, a freezing saccule ablation catheter and an electric signal detection catheter. In the process of freezing balloon ablation, the plugging condition of the pulmonary vein opening needs to be judged. The occlusion of the pulmonary vein ostium represents the contact of the cryoballoon with the tissue of the pulmonary vein ostium, which greatly affects the success rate of the procedure. In the prior art, the contrast agent is injected into the pulmonary vein from the far end of the freezing saccule, and if the contrast agent is kept in the pulmonary vein and does not enter the left atrium, the contrast agent indicates that the opening of the pulmonary vein is completely blocked by the freezing saccule. In addition, the occlusion condition of the freezing saccule to the pulmonary vein orifice can be judged based on color ultrasound through an intracardiac echocardiography (ICE for short) catheter, if the occlusion condition is not good, blood flows in a gap between the blood and the pulmonary vein orifice, and then different colors are displayed on an ultrasonic image, and if the occlusion condition is good, different colors cannot be seen. However, this approach requires the re-insertion of a separate ICE catheter, which significantly increases the economic burden on the patient.

Therefore, how to provide a scheme capable of acquiring pulmonary vein occlusion conditions rapidly, safely, harmlessly, accurately and at low cost is a technical problem to be solved in the field.

SUMMERY OF THE UTILITY MODEL

The application aims to provide a mapping electrode catheter capable of evaluating pulmonary vein occlusion conditions, and solves the technical problems that in the prior art, the pulmonary vein occlusion judgment mode influences human health and is high in cost.

To achieve the above object, the present application provides a mapping electrode catheter for evaluating pulmonary vein occlusion, comprising: the device comprises an ablation plugging device, a sheath tube, an electric signal detection catheter and a plugging detection processor; wherein,

the ablation occluder is an expansion occluder which expands during inflation or under the control of a signal, and is provided with an internal guide wire cavity; one end of the ablation plugging device is pushed out of the sheath tube, and the other end of the ablation plugging device is provided with an internal guide wire cavity outlet;

the sheath is a catheter with a hollow inner cavity, and the proximal part of the sheath is connected with the ablation occluder;

the proximal part of the electric signal detection catheter penetrates out of the outlet of the internal guide wire cavity, the distal part of the electric signal detection catheter is a bent electrode catheter, and a mapping electrode and an image collector are arranged in the inner cavity of the bent electrode catheter;

and the plugging detection processor is connected with the image collector and receives the collected image of the image collector. And the plugging detection processor receives the collected image of the image collector, processes the collected image according to a preset processing strategy and displays the processed image.

Optionally, wherein the ablation occluder is a cryoballoon.

Optionally, wherein the image collector is an ultrasonic transducer.

Optionally, wherein the distal end of the electrical signal detection catheter is bent into a loop.

Optionally, wherein the mapping electrodes and image collectors are distributed in a spaced relationship on the electrical signal detection catheter.

Optionally, wherein the tail end of the electrical signal detection catheter is bent into a J-shape, the middle portion is bent into a ring, and the mapping electrode is located at the middle ring portion.

Optionally, wherein the image collector is located at a head end portion of the distal end of the electrical signal detection catheter.

Optionally, wherein the middle part of the electric signal detection conduit is bent into a ring shape, and the tail end is bent into a J shape; the mapping electrode is positioned on the middle annular part, and the image collector is positioned on the head end part of the far end of the electric signal detection catheter.

Optionally, wherein the mapping electrodes and the image collectors are distributed on the electrical signal detection catheter at intervals, and more than or equal to two image collectors are disposed between adjacent mapping electrodes.

Optionally, wherein the occlusion detection processor comprises: the image processing unit and the ablation plugging control unit;

the image processing unit is connected with the image collector, receives the collected image of the image collector, processes the collected image according to a preset processing strategy and displays the processed image;

the ablation plugging control unit is connected with the image processing unit and the ablation plugging device, receives the processed acquired image, compares the acquired image with a pre-stored standard image and controls the ablation plugging device to start cryoablation when the plugging condition is judged to be good.

The mapping electrode catheter capable of evaluating the pulmonary vein occlusion condition has the following beneficial effects:

(1) the mapping electrode catheter capable of evaluating the pulmonary vein occlusion condition integrates the ultrasonic probe on the electric signal detection catheter, utilizes the ultrasonic probe to collect images for processing and synthesizing, judges the occlusion condition of the cryoballoon in the pulmonary vein based on color ultrasonic Doppler, replaces a contrast agent injection to judge the occlusion mode, reduces the irradiation time of X rays, eliminates the influence of the contrast agent injection on the body health of patients and doctors and patients, and improves the safety of the electrode catheter.

(2) The mapping electrode catheter capable of evaluating the pulmonary vein plugging condition integrates the ultrasonic probe on the electric signal detection catheter, utilizes the ultrasonic probe to collect images for processing and synthesizing, judges the plugging condition of the freezing balloon in the pulmonary vein based on color ultrasonic Doppler, reduces the insertion quantity of the catheter, relieves the pain of a patient and reduces the treatment cost compared with an ICE (Integrated Circuit emphasis) plugging judgment mode.

Drawings

In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings needed to be used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments described in the present application, and other drawings can be obtained by those skilled in the art according to the drawings.

Fig. 1 is a schematic illustration of a mapping electrode catheter inserted into the left atrium for assessment of pulmonary vein occlusion in an embodiment of the invention;

fig. 2 is a schematic structural view of a mapping electrode catheter capable of evaluating pulmonary vein occlusion according to embodiment 1 of the present invention;

fig. 3 is a schematic structural view of a second mapping electrode catheter for evaluating pulmonary vein occlusion according to embodiment 1 of the present invention;

fig. 4 is a schematic structural view of a third mapping electrode catheter for evaluating pulmonary vein occlusion according to embodiment 1 of the present invention;

fig. 5 is a schematic view of blood flow after a mapping electrode catheter for evaluating pulmonary vein occlusion conditions is inserted into the left atrium in embodiment 2 of the present invention;

fig. 6 is a schematic cross-sectional view of pulmonary vein occlusion after a mapping electrode catheter that can evaluate pulmonary vein occlusion in embodiment 3 of the present invention is inserted into the left atrium;

fig. 7 is a schematic cross-sectional view of a pulmonary vein occlusion that is poor after a mapping electrode catheter that can evaluate the pulmonary vein occlusion situation is inserted into the left atrium in embodiment 4 of the present invention;

fig. 8 is a schematic structural view of an electrical signal detection catheter of a mapping electrode catheter that can be used to assess pulmonary vein occlusion in example 5 of the present invention;

fig. 9 is a schematic structural view of a connection between an electrical signal detection catheter of a mapping electrode catheter, an ablation occluder and a sheath for evaluating pulmonary vein occlusion in example 5 of the present invention;

fig. 10 is a schematic diagram of a shape transition of an electrical signal detection catheter of a mapping electrode catheter that can be used to assess pulmonary vein occlusion in example 5 of the present invention;

fig. 11 is a schematic diagram of electronic focusing and electronic deflection of an ultrasonic phased array of an ultrasonic probe in an electrical signal detection catheter according to embodiment 5 of the present invention.

Detailed Description

The technical solutions in the embodiments of the present application are clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are some, but not all, embodiments of the present application. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.

Example 1

As shown in fig. 1 and 2, fig. 1 is a schematic diagram of a mapping electrode catheter inserted into the left atrium for evaluating pulmonary vein occlusion in an embodiment of the present invention; fig. 2 is a schematic structural diagram of a mapping electrode catheter capable of evaluating pulmonary vein occlusion according to an embodiment of the present invention. Existing cryoballoon ablation procedures generally include the following steps in the left atrium:

step 1, bending the electric signal detection catheter into a ring shape, and pushing the ring shape to a pulmonary vein detection potential.

And 2, pushing the cryoablation balloon catheter out of the adjustable bent sheath, and inflating and expanding the left atrium.

And 3, pushing the cryoablation balloon catheter to the pulmonary vein opening, and plugging the pulmonary vein opening.

And 4, injecting a contrast agent (which can be developed under X-ray) to judge the plugging condition of the pulmonary vein orifice.

And 5, injecting cryogenic fluid into the balloon for ablation if the blocking condition is good (the contrast agent does not flow from one side of the balloon to the other side).

And 6, after the ablation is finished, deflating the freezing saccule, and withdrawing the freezing saccule and the electric signal detection catheter into the sheath.

In addition to the above-mentioned manner, whether the cryoballoon completely blocks the pulmonary vein can be determined by measuring the blood pressure and temperature changes. Besides, the temperature and the strain at the contact part of the freezing saccule and the tissue can be measured by using a light sensor, and the temperature and the strain can be measured by the shift of the wavelength by using the relation between the temperature change and the change of the axial strain and the shift of the wavelength. However, the accuracy of these methods for determining pulmonary vein occlusion needs to be improved. In the embodiment, the ultrasonic image is acquired through the image acquisition image, the blocking condition of the cryoballoon catheter is judged based on a Doppler method, and the accuracy and the safety are greatly improved compared with the mode in the prior art. Specifically, this an electric signal detection pipe for pulmonary vein occlusion detection includes: an ablation occluder 101, a sheath 102, an electrical signal detection catheter 103 and an occlusion detection processor 104.

The ablation occluder 101 is an expansion occluder which expands during inflation or under the control of signals, and is provided with an internal guide wire cavity; one end of the ablation plugging device is pushed out from the sheath tube 102, the other end of the ablation plugging device is provided with an internal guide wire cavity outlet, the internal guide wire cavity outlet is an opening of the internal guide wire cavity at the end part, the electric signal detection catheter 103 is located in the internal guide wire cavity, and the internal guide wire cavity is penetrated out through the internal guide wire cavity outlet.

The sheath 102, which is a catheter having a hollow lumen, has its proximal portion connected to the ablation occluder 101. And the electric signal detection catheter 103 is provided with a proximal end part 134 which penetrates out of the outlet of the internal guide wire cavity, a distal end part which is a bent electrode catheter, and a mapping electrode 131 and an image collector 132 are arranged in the inner cavity of the bent electrode catheter 133. And the occlusion detection processor 104 is connected with the image collector 132 in a wireless or wired manner, receives the collected image of the image collector, and displays the image after processing according to a preset processing strategy. The wireless communication connection mode may be a connection mode through wireless communication such as bluetooth, Zigbee, Near Field Communication (NFC), WiFi, mobile network (3G, 4G, or 5G), and the like.

In some alternative embodiments, the ablation occluder is a cryoballoon.

By using the mapping electrode catheter of the present embodiment capable of evaluating pulmonary vein occlusion, the above step 4 becomes: the occlusion detection processor processes an ultrasonic image acquired by an image acquirer on the electric signal detection catheter according to a preset standardized processing strategy and displays the ultrasonic image, medical staff see that a part with poor occlusion condition has obvious color difference based on the image and judge that the occlusion is not good, and the position of the freezing balloon catheter needs to be adjusted based on the displayed image; if the medical staff sees that the part of shutoff does not have the color difference based on the image, judges that the shutoff condition is good, can start the cryoablation.

In some optional embodiments, when the plugging is not good, the plugging detection processor analyzes the conditions of the freezing balloon catheter and the part to be plugged according to the obtained plugging part image, compares the obtained plugging part image with a pre-stored standard plugging image to obtain a plugging difference parameter, controls the position of the freezing balloon catheter to be adjusted according to the plugging difference parameter until the freezing balloon catheter is detected to plug the part to be plugged completely, and displays the image which is plugged completely. So through automatic intelligent detection and control, the automatic adjustment shutoff condition when freezing sacculus pipe shutoff is bad has reduced medical personnel's operation, has promoted the efficiency and the speed of treatment.

In some optional embodiments, the occlusion detection processor may further be configured to detect an environmental parameter of image acquisition, acquire an image acquisition parameter according to the environmental parameter, a pre-stored environmental parameter and an image acquisition parameter comparison table, and control image acquisition by using the acquired image acquisition parameter, so as to facilitate image acquisition under the best image acquisition condition, thereby improving accuracy of detection and determination of the occlusion condition.

In some optional embodiments, the image collector is an ultrasound transducer. Preferably, the frequency range of the ultrasonic transducer of the present embodiment may be between 5MHz and 40MHz, wherein typical frequencies are: 5MHz, 8MHz, 9MHz, 10MHz, 12MHz, 20MHz, 40 MHz.

In some alternative embodiments, the distal end of the electrical signal detection catheter is bent into a loop, and the mapping electrodes and the image collector are distributed on the electrical signal detection catheter at intervals.

In some alternative embodiments, the image collector (e.g., ultrasound transducer) may be a rectangular parallelepiped or other shape (e.g., polyhedron) that is easy to be placed in the electrical signal detection catheter, so that it can be embedded in the electrical signal detection catheter but cannot slide freely. The maximum distance between different points on the image collector and the mapping electrode does not exceed the diameter of the electric signal detection catheter, and optionally, the ratio of the maximum distance to the diameter of the electric signal detection catheter is between 0.5 and 1, and the arrangement basically ensures that the image collector and the mapping electrode can be embedded into the electric signal detection catheter.

Typically, the diameter of the electrical signal detection catheter is about 1mm, and in this case, the number of mapping electrodes can be set to be between 3 and 20, and more preferably, 8 or 10, and the image collectors and the mapping electrodes are distributed on the electrical signal detection catheter at intervals. Typically, the length of a single mapping electrode is about 1 mm. The distance between the electrodes is 4.1mm (8) or 5.8mm (10), and the length and size of the mapping electrode can be set according to the diameter of the electric signal detection catheter. And image collectors and mapping electrodes with proper quantity and diameter can be arranged according to the diameter of the electric signal detection catheter.

In some alternative embodiments, as shown in fig. 3, a schematic structural diagram of a second mapping electrode catheter capable of evaluating pulmonary vein occlusion in the present embodiment is shown. Unlike in fig. 2, the tail end of the electrical signal detection catheter is bent in a J-shape, the middle portion is bent in a ring shape, the mapping electrode 131 is located in the middle ring portion, and the image collector 132 is located in the head end portion of the distal end of the electrical signal detection catheter.

In some alternative embodiments, the middle portion of the electrical signal detection conduit is bent into a ring shape, and the tail end is bent into a J shape; the mapping electrode is positioned on the middle annular part, and the image collector is positioned on the head end part of the far end of the electric signal detection catheter.

In some optional embodiments, the mapping electrodes and the image collectors are distributed on the electrical signal detection catheter at intervals, and more than or equal to two image collectors are arranged between adjacent mapping electrodes.

In some alternative embodiments, as shown in fig. 4, a schematic structural diagram of a third mapping electrode catheter capable of evaluating pulmonary vein occlusion in this embodiment is shown. An occlusion detection processor 104 comprising: an image processing unit 141 and an ablation occlusion control unit 142.

And the image processing unit 141 is connected with the image collector 132, and receives the collected image of the image collector, and displays the collected image after processing according to a preset processing strategy.

And the ablation plugging control unit 142 is connected with the image processing unit 141 and the ablation plugging device 101, receives the processed collected image, compares the processed collected image with a pre-stored standard image, and controls the ablation plugging device to start cryoablation when the plugging condition is judged to be good.

The ablation plugging control unit processes the result judgment obtained by collecting images based on the image processing unit, automatically controls the ablation plugging device to perform cryoablation under the condition of good plugging, greatly reduces the operation of medical personnel, and improves the intelligence of the electric signal detection catheter for pulmonary vein plugging detection. Optionally, when the occlusion is good, a cryoablation starting instruction is generated to display and a prompt message (such as a warning sound) is generated, countdown is started according to a preset countdown strategy, and cryoablation is automatically started after the countdown is finished. And stopping starting the cryoablation after receiving a stop instruction before the countdown is finished.

Example 2

As shown in fig. 1 to 5, fig. 5 is a schematic diagram of blood flow after a mapping electrode catheter capable of evaluating pulmonary vein occlusion in the present embodiment is inserted into the left atrium, the pulmonary vein blood flows to the left atrium according to the direction a in the figure, and the ablation occluder 101 expands to occlude the pulmonary vein when inflated or controlled by a signal, so as to occlude the pulmonary vein and prevent blood from leaving the pulmonary vein and entering the left atrium of the heart of the patient. Alternatively, sensors (e.g., pressure sensors) may be added to record blood pressure measurements for occlusion assessment, and the sensors may be disposed around the periphery of the electrical signal sensing catheter 103 in a band-like arrangement. Taking a pressure sensor as an example for explanation, detecting and storing a pressure range under the condition that the pulmonary vein is completely blocked, a pressure range under the condition that the pulmonary vein is partially blocked and a pressure range under the condition that the pulmonary vein is completely unblocked in advance, measuring an actual pulmonary vein blocking pressure value and comparing the actual pulmonary vein blocking pressure value with the pressure range during actual detection, and judging that the pulmonary vein is completely blocked when the actual pressure range falls into the pressure range under the condition that the pulmonary vein is completely blocked; when the actual pressure range falls into the pressure range under the condition that the pulmonary vein is not blocked completely, judging that the pulmonary vein is not blocked completely; when the actual pressure range falls in the pressure range under the pulmonary vein partial plugging, the pulmonary vein partial plugging is judged, and when the pulmonary vein partial plugging occurs, the ablation plugging device 101 can be repositioned, and the measured value is obtained until the pulmonary vein is completely plugged. The electric signal detection catheter 103 is positioned in the pulmonary vein for mapping pulmonary vein tissues and sensing blood pressure and other conditions in the distal end of the pulmonary vein, an ultrasonic image is shot and displayed in a color, line or sound mode, and medical staff judges the blocking condition based on the display and then performs subsequent cryoablation operation.

Example 3

As shown in fig. 1 to 5 and 6, fig. 6 is a schematic cross-sectional view of a pulmonary vein occlusion after a mapping electrode catheter that can evaluate the pulmonary vein occlusion situation in this embodiment is inserted into the left atrium. The cross-sectional view in fig. 6 is a cross-sectional view perpendicular to the direction a in fig. 5, and may be presented to the doctor in the form of color, lines, sounds, or the like. 601 is irregular pulmonary vein wall, 602 is the outer wall of the ablation occluder, the ablation occluder is inflated or is controlled by signals to expand to completely occlude the pulmonary vein, and at the moment, the pulmonary vein has no blood flow to left atrium. An image collector based on the electric signal detection catheter collects an image of no blood flowing from the pulmonary veins to the left atrium. If medical personnel see that the plugging condition of the plugged part is good based on the image, the cryoablation can be started. Or automatically starting the cryoablation after judging that the pulmonary vein occlusion condition is good. Or automatically starting cryoablation countdown after the pulmonary vein occlusion condition is judged to be good, displaying a pulmonary vein occlusion acquisition image, and automatically starting cryoablation when the starting of the cryoablation is not cancelled after the countdown is finished.

Example 4

As shown in fig. 1 to 5 and 7, fig. 7 is a schematic cross-sectional view of a pulmonary vein occlusion failure after insertion of a mapping electrode catheter into the left atrium, which can evaluate pulmonary vein occlusion in this embodiment. The cross-sectional view in fig. 7 is a cross-sectional view perpendicular to the direction a in fig. 5, and may be presented to the doctor in the form of color, lines, sounds, or the like. 701 is irregular pulmonary vein wall, 702 is the outer wall of the ablation occluder, the ablation occluder is inflated or is controlled by signals to expand and not completely occlude pulmonary veins, and at the moment, pulmonary vein blood 703 flows from the periphery of the outer wall of the ablation occluder to the left atrium. The image collector based on the electric signal detection catheter collects the image that blood flows from the pulmonary veins to the left atrium, and at the moment, the cryoablation cannot be started. Medical personnel are required to judge and adjust the ablation occluder according to the acquired image to reposition until the pulmonary vein is completely occluded.

Example 5

Fig. 8 is a schematic diagram of an electrical signal detection catheter of a mapping electrode catheter for evaluating pulmonary vein occlusion in accordance with the present embodiments, as shown in fig. 1-10; fig. 9 is a schematic view of an electrical signal detection catheter of a mapping electrode catheter with an ablation occluding device and sheath connection for assessing pulmonary vein occlusion in this embodiment; fig. 10 is a schematic view of a shape transition of an electrical signal detection catheter of a mapping electrode catheter in accordance with an embodiment of the present disclosure that can assess pulmonary vein occlusion. The electric signal detection catheter includes: a traction catheter 801 and a bent electrode catheter 802, wherein a mapping electrode and an image collector are arranged in the inner cavity of the bent electrode catheter 802. Optionally, there are 8 mapping electrodes evenly distributed on the surface of the curved electrode catheter, with the image collector located between the mapping electrodes. The electric signal detection catheter is penetrated out of the cavity inside the ablation occluder 101 and the sheath 102, and the distal end tip is the distal end tip of the ablation occluder in the figure. The traction catheter 801 and the bending electrode catheter 802 of the electrical signal detection catheter are connected by a connecting member 803. The transition from the straight configuration to the curved annular configuration of the electrical signal detection conduit can be achieved. The probe has a plurality of installation modes, the number of the probes is more than or equal to 1, when the number of the probes is 1, the probes can be controlled to move in the electric signal detection catheter by adjusting the probe through a controller, or the probe is automatically controlled to move according to a preset movement control strategy. More preferably, the number of probes is 2 or more, and practically 1 or more probes can be placed in each void between mapping electrodes.

Image collector (ultrasonic probe)

For an image collector (an ultrasonic probe), a phased array transducer is used for rapidly moving an acoustic beam to image a detected organ in medical ultrasonic imaging. The working principle of ultrasonic phased array transducers is based on the huygens-fresnel principle. Ultrasonic phased array technology, similar to phased array radar, sonar and other wave physics applications, relies on Huyghens-Fresnel principles: any wave front of the wave field is equivalent to a secondary wave source; the secondary wavefield may be computed by superposition interference of spherical wavelets generated at points on the wavefront and displaying a fidelity (or geometrically corrected) echo image, which is similar to a medical ultrasound image of the internal structure of the material being generated.

When the array elements are excited by pulse signals with the same frequency, the sound waves emitted by the array elements are coherent waves, namely the sound pressure amplitude of some points in the space is enhanced due to the in-phase superposition of the sound waves, and the sound pressure amplitude of other points is weakened due to the opposite-phase cancellation of the sound waves, so that a stable ultrasonic field is formed in the space. The structure of the ultrasonic phased array transducer is an array formed by a plurality of piezoelectric wafers which are mutually independent, each wafer is called as a unit, each unit is controlled and excited by an electronic system according to a certain rule and a certain time sequence, and ultrasonic waves emitted by each unit in the array are superposed to form a new wave front, as shown in figure 11, the ultrasonic phased array transducer is a schematic diagram of electronic focusing and electronic deflection of an ultrasonic phased array of an ultrasonic probe in an electric signal detection catheter. Similarly, when receiving the reflected wave, the receiving unit is controlled according to a certain rule and time sequence to perform signal synthesis and display. The angle, focus position and focal spot size of the generated beam can thus be controlled by individually controlling the firing time of each wafer in the phased array probe.

Ultrasonic inspection requires imaging of a region within an object for which an acoustic beam scan must be performed. The common fast scanning methods are mechanical scanning and electronic scanning, which can obtain image display, and are usually combined together in the ultrasonic phased array imaging technology. The ultrasonic phased array imaging technology is a technology which changes the phase relation when sound waves transmitted (or received) by each array element reach (or come from) a certain point in an object by controlling the time delay of an excitation (or receiving) pulse of each array element in a transducer array, realizes the change of a focus point and the azimuth of a sound beam, and completes imaging. Each array element in the ultrasonic phased array is excited by the same pulse with different delay time, and the deflection angle and the focus are controlled by controlling the delay time. In practice, a fast deflection of the focus makes it possible to perform two-dimensional imaging of the test piece.

The key of the ultrasonic phased array technology is to adopt a brand-new method which occurs in the receiving of ultrasonic waves, adopt a plurality of precise, complex, extremely small-sized and mutually independent piezoelectric wafer arrays (such as 36, 64 or even up to 128 wafers assembled in a probe shell) to generate and receive ultrasonic beams, and control the phase and time sequence of each high-frequency excitation pulse of the piezoelectric wafer arrays through powerful software and electronic methods so as to enable the high-frequency excitation pulses to interfere with each other and overlap to generate an ultrasonic field with a controllable shape, thereby obtaining a pre-desired wave front, a wave beam incident angle and a focus position. Thus, ultrasonic phased arrays are essentially implemented with phase controllable transducer arrays.

Each piezoelectric wafer of the ultrasonic phased array probe can independently receive signal control (pulse and time change), each unit in the array probe is sequentially excited in different time through software control, waves excited by each wafer are in sequence due to different excitation sequences, and the waves are overlapped to form a new wave front, so that the wave front of the ultrasonic waves can be focused and controlled to a specific direction, ultrasonic beams can be radiated at different angles, and the focusing (electronic focusing) of the same probe at different depths can be realized. Furthermore, electronically determining the phase sequence and speed of successive excitations for the array allows the ultrasound beam from a probe fixed in position to be dynamically "swept" or "swept" through a selected range of beam angles without requiring manual manipulation of the probe. Key characteristics of phased array probes include: electronic focal length adjustment, electronic linear scanning, and electronic beam steering/angling.

Different combinations of wafers of ultrasonic phased array transducers form different phased arrays, and there are currently three main types of arrays: linear arrays (wafers are linearly distributed in the probe in a spaced-apart manner), surface-shaped (two-dimensional matrix) arrays, and circular (annular) arrays. The probe characteristic parameters of the phased array ultrasonic wave comprise: frequency, wavelength, total number of wafers in the array, total aperture of sound field control direction, wafer length, non-control direction aperture, width of each wafer, spacing between two active wafers, and wafer dicing gap. Parameters of the wedges or shoes on the probe include: speed of sound, angle, first wafer height, first wafer offset, etc. The general characteristics that can be reached of present ultrasonic phased array probe: the working frequency is as follows: 1MHz-7.5MHz (up to 10 MHz); piezoelectric material: most of the piezoelectric materials are composite piezoelectric materials, and organic polymer piezoelectric materials are also adopted, and the crystal size can reach 0.8 x 0.8mm or less; number of voltage cells: 16-256 units (16, 32, 64 and 128 units are currently common); piezoelectric unit interval: the minimum can reach 0.1 mm; bandwidth (-6 dB): typically 60% to 80%; cell sensitivity deviation: can reach +/-2 dB.

While the preferred embodiments of the present application have been described, additional variations and modifications in those embodiments may occur to those skilled in the art once they learn of the basic inventive concepts. Therefore, it is intended that the appended claims be interpreted as including preferred embodiments and all alterations and modifications as fall within the scope of the application. It will be apparent to those skilled in the art that various changes and modifications may be made in the present application without departing from the spirit and scope of the application. Thus, if such modifications and variations of the present application fall within the scope of the claims of the present application and their equivalents, the present application is intended to include such modifications and variations as well.

Claims (10)

1. A mapping electrode catheter for assessing pulmonary vein occlusion, comprising: the device comprises an ablation plugging device, a sheath tube, an electric signal detection catheter and a plugging detection processor; wherein,

the ablation occluder is an expansion occluder which expands during inflation or under the control of a signal, and is provided with an internal guide wire cavity; one end of the ablation plugging device is pushed out of the sheath tube, and the other end of the ablation plugging device is provided with an internal guide wire cavity outlet;

the sheath is a catheter with a hollow inner cavity, and the proximal part of the sheath is connected with the ablation occluder;

the proximal part of the electric signal detection catheter penetrates out of the outlet of the internal guide wire cavity, the distal part of the electric signal detection catheter is a bent electrode catheter, and a mapping electrode and an image collector are arranged in the inner cavity of the bent electrode catheter;

and the plugging detection processor is connected with the image collector and receives the collected image of the image collector.

2. The mapping electrode catheter of claim 1, wherein the ablation occluder is a cryoballoon.

3. The mapping electrode catheter of claim 1, wherein the image collector is an ultrasound transducer.

4. The mapping electrode catheter of claim 1, wherein the electrical signal detects that the distal end of the catheter is bent into a loop.

5. The catheter of claim 1 or 4, wherein the mapping electrodes are spaced apart from the image collector on the electrical signal detection catheter.

6. The mapping electrode catheter for assessing pulmonary vein occlusion of claim 1, wherein the electrical signal detection catheter is bent into a J-shape at a tail end and into a ring shape at a middle portion, and the mapping electrode is located at the middle ring portion.

7. The mapping electrode catheter of claim 1 or 6, wherein the image collector is located at a distal tip portion of the electrical signal detection catheter.

8. The mapping electrode catheter capable of assessing pulmonary vein occlusion of claim 1, wherein the electrical signal detection catheter is bent in a ring shape at a middle portion and in a J shape at a tail end; the mapping electrode is positioned on the middle annular part, and the image collector is positioned on the head end part of the far end of the electric signal detection catheter.

9. The catheter of claim 1, wherein the mapping electrodes and the image collectors are spaced apart from each other on the electrical signal detection catheter, and more than or equal to two image collectors are disposed between adjacent mapping electrodes.

10. The mapping electrode catheter of claim 1, wherein the occlusion detection processor comprises: the image processing unit and the ablation plugging control unit;

the image processing unit is connected with the image collector, receives the collected image of the image collector, processes the collected image according to a preset processing strategy and displays the processed image;

the ablation plugging control unit is connected with the image processing unit and the ablation plugging device, receives the processed acquired image, compares the acquired image with a pre-stored standard image and controls the ablation plugging device to start cryoablation when the plugging condition is judged to be good.

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