CN221205602U - Puncture system and ultrasonic ablation system - Google Patents

Abstract

The utility model provides a puncture system and an ultrasonic ablation system, wherein the puncture system comprises: the device comprises a penetrating unit, a connecting pipe sleeved on part of the penetrating unit, and an energy assembly arranged inside the connecting pipe and connected with the penetrating unit; the puncturing unit includes: the connecting part extends along the axial direction away from one end of the connecting pipe to form a conical tip with a tapered outer diameter; the energy assembly includes: the energy unit is arranged on the base and at least comprises an ablation unit. According to the utility model, in the process of ablating specific target tissues, damage to peripheral non-target tissues is avoided, and the safety is improved.

Description

Puncture system and ultrasonic ablation system

Technical Field

The utility model relates to the technical field of medical instruments, in particular to a puncture system and an ultrasonic ablation system.

Background

Medical intervention devices with ablation functionality have gained widespread acceptance in medical diagnostics, image guidance and control of diagnostics, therapy and surgery, and the need for effective imaging. The aforementioned medical intervention devices must be performed in complex networks of stenosed and inaccessible body cavities (e.g. the blood vessels of the cardiovascular and neurovascular systems, the airway tree of the lungs, and the gastrointestinal tract, bile and urinary tract) or in the narrow spaces of naturally or surgically created body cavities. Image guidance is intended to identify and locate a particular target within a patient's body to allow for accurate placement of medical instruments or tools within the target to perform medical procedures using the tools while avoiding anatomical risk structures. Many medical tools have specific intended uses for specific medical procedures, such as: an injection needle for delivering a therapeutic agent; biopsy instruments that collect tissue samples, such as aspiration needles, biopsy forceps, or brushes; surgical instruments for resecting diseased tissue; and depositing Radio Frequency (RF), microwave (MW), laser and/or other energy or cryogenically cooled tissue to ablate the diseased tissue.

Medical intervention equipment (such as a microwave ablation needle, a radio frequency ablation needle and the like) with an ablation function in the prior art is contacted with specific target tissues through an electrode, ablation is realized on the specific target tissues which are contacted with the electrode by means of heating of the electrode, and the tissue temperature which is closer to the electrode is higher, so that the electrode is easy to damage non-target tissues (such as blood vessels and the like) around the electrode in the process of ablating the specific target tissues, and the safety is low. Meanwhile, medical intervention equipment with puncture, imaging and ablation functions does not exist in the prior art, so that the puncture position of the medical intervention equipment in human tissues is inconvenient to observe in real time, a doctor needs to repeatedly observe human tissue images, the operation steps of the doctor are increased, and the operation time is prolonged.

In view of the above, there is a need for improvements in medical intervention devices in the prior art to address the above-described problems.

Disclosure of utility model

The utility model aims to disclose a puncture system and an ultrasonic ablation system, which are used for solving the safety problem that the medical intervention equipment in the prior art is easy to damage peripheral non-target tissues in the process of ablating specific target tissues. But also solves the technical problems that the doctor needs to repeatedly observe the images of human tissues and the operation steps of the doctor are increased because the puncture, imaging and ablation functions are not provided.

To achieve one of the above objects, the present utility model provides a puncture system comprising: the device comprises a penetrating unit, a connecting pipe sleeved on part of the penetrating unit, and an energy assembly arranged inside the connecting pipe and connected with the penetrating unit;

The penetration unit includes: a connecting portion extending axially away from one end of the connecting tube to form a tapered tip with a tapered outer diameter;

The energy assembly includes: the energy unit is arranged on the base and at least comprises an ablation unit.

As a further improvement of the present invention, an angle α formed between an extending direction of the tapered surface included in the tapered tip and an axis of the tapered tip is 2.5 ° or more and 37.5 ° or less.

As a further improvement of the present invention, the diameter of the tapered tip is 0.5mm or more and 3mm or less, and the axial length of the tapered tip is 3mm or more and 10mm or less.

As a further improvement of the present invention, the connecting portion is configured to accommodate a rotation space of at least part of the base, and a gap for axial rotation of the base relative to the connecting portion is formed between the base and the rotation space.

As a further improvement of the invention, the base is concavely arranged radially inwards to form a partition plate part, and the partition plate part is provided with an energy unit;

The energy unit includes: the imaging unit and the ablation unit are arranged on two sides of the partition plate part in a circumferential direction in an opposite manner;

the plane of the imaging unit is parallel to the plane of the ablation unit, or an included angle formed by the plane of the imaging unit and the plane of the ablation unit is more than 0 degrees and less than or equal to 90 degrees.

As a further development of the invention, the imaging unit is arranged at least partially axially opposite to the ablation unit or the imaging unit is arranged axially spaced apart from the ablation unit.

As a further improvement of the present invention, both the side of the partition plate portion attached to the imaging unit and the side of the partition plate portion attached to the ablation unit are provided with isolation layers for isolating the ultrasonic signals between the imaging unit and the ablation unit.

As a further improvement of the present invention, the diaphragm portion is configured as a solid plate-like structure, or a cavity with gas filled or a cavity filled with a wave-absorbing material or a vacuum cavity is configured inside the diaphragm portion to isolate an ultrasonic signal between the imaging unit and the ablation unit.

Based on the same inventive concept, the utility model also discloses an ultrasonic ablation system, comprising: a multilayer catheter, the puncture system disclosed in any one of the above utility models disposed at the distal end of the multilayer catheter, and a circulation system and a driving system disposed in this order at one end of the multilayer catheter away from the puncture system;

The circulation system is in communication with the multi-layered catheter for delivering fluid to the puncture system, and the drive system drives the base to axially rotate relative to the connection.

As a further improvement of the present invention, the circulation system includes: the circulating cabin body is penetrated by the multilayer conduit, and the circulating cabin body is axially and continuously formed in the circulating cabin body and is communicated with the liquid outlet cavity and the liquid inlet cavity of the multilayer conduit, and the liquid outlet pipe and the liquid inlet pipe are respectively communicated with the liquid outlet cavity and the liquid inlet cavity.

As a further improvement of the present invention, the multilayer catheter comprises: the outer layer catheter is coaxially arranged in the inner layer catheter of the outer layer catheter, and the transmission shaft axially penetrates through the inner layer catheter and is fixedly connected with one end, far away from the connecting part, of the base;

One end of the transmission shaft, which is far away from the connecting part, extends out of the circulation cabin body and is connected with the driving system, and the driving system drives the transmission shaft to rotate so as to drive the base to axially rotate relative to the connecting part.

As a further improvement of the invention, the liquid inlet cavity is radially inwards convexly provided with a first convex part, and the liquid outlet cavity is radially inwards convexly provided with a second convex part;

The inner layer catheter is far away from one end of the puncture system and axially abuts against the first convex part so as to isolate the liquid inlet cavity from the liquid outlet cavity, and the outer layer catheter is far away from one end of the puncture system and axially abuts against the second convex part.

As a further improvement of the invention, the two ends of the connecting pipe along the axial direction are respectively sleeved on the connecting part and the outer-layer catheter and are enclosed to form a cooling cavity for accommodating the energy component;

A first channel for liquid circulation is formed between the inner side wall of the inner layer conduit and the outer side wall of the transmission shaft, and liquid in the liquid inlet cavity flows to the cooling cavity through the first channel;

A second channel for liquid circulation is formed between the outer side wall of the inner layer catheter and the inner side wall of the outer layer catheter, and liquid in the cooling cavity flows to the liquid outlet cavity through the second channel.

Compared with the prior art, the utility model has the beneficial effects that:

The skin is pierced through the conical tip to enter the patient, the specific target tissue is isolated from the ablation unit through the engagement tube, the ablation unit is prevented from directly contacting the specific target tissue, the ablation unit generates heat through ultrasonic waves and focuses the heat deep in the specific target tissue, the temperature at the focal point is highest, so that enough heat is generated at the focal point to ablate the specific target tissue, damage to non-target tissues (such as blood vessels and the like) is avoided, and safety is improved.

Drawings

FIG. 1 is a perspective view of an ultrasound ablation system incorporating a puncture system of the present utility model;

FIG. 2 is an axial cross-sectional view of an ultrasound ablation system with the drive system omitted;

FIG. 3 is an exploded view of the piercing tip along the axis P in FIG. 1;

FIG. 4 is a cross-sectional view of one embodiment of a piercing tip taken longitudinally along the P-axis;

FIG. 5 is a cross-sectional view of another embodiment of the piercing tip taken longitudinally along the P-axis;

FIG. 6 is an enlarged view of a portion of FIG. 2 at box F;

FIG. 7 is an enlarged view of a portion of FIG. 6 at circle H;

FIG. 8 is a partial enlarged view at box D of FIG. 2;

FIG. 9 is an enlarged view of a portion of FIG. 2 at box E;

FIG. 10 is an enlarged view of a portion of FIG. 2 at box C;

Fig. 11 is a partial enlarged view at a box G in fig. 10.

Detailed Description

The present utility model will be described in detail below with reference to the embodiments shown in the drawings, but it should be understood that the embodiments are not limited to the present utility model, and functional, method, or structural equivalents and alternatives according to the embodiments are within the scope of protection of the present utility model by those skilled in the art.

In particular, in the following embodiments, the term "axial direction" refers to the direction indicated by the central axis P in fig. 3.

Examples of the energy form of the ablation unit 424 include piezoelectric crystals, radio frequency electrodes, and microwave generating elements. Taking a piezoelectric wafer as an example, the ablation unit 424 is made of a piezoelectric wafer, and the shape of the piezoelectric wafer is not limited, for example, a common sheet shape, a ring shape, a semi-ring shape, an arc shape, and the like; using the piezoelectric wafer thermal effect, the piezoelectric wafer is activated by a control system (not shown) to operate, the thermal energy generated by which is transferred over a period of time that may be between 10 seconds and 10 minutes; the heat temperature can reach more than 50 ℃, and the heat generated by the heat generator can achieve the effect of thermal ablation of local tissues of a human body.

In this embodiment, the ablation unit 424 is preferably in a sheet shape, and in order to further increase heat concentration at the thermal focus or change the position of the focus, shorten the treatment time, an acoustic beam steering layer (not shown) is disposed on the outer layer of the piezoelectric wafer, and the acoustic beam steering layer may be disposed in a certain arc, and the setting of the arc should not be too large, preferably controlled within 10 ° to change the position of the focus, or concentrate more energy. An ultrasonic imaging transducer may also be employed for imaging unit 422, which may include a backing layer, a piezoelectric layer, a matching layer; the ultrasound imaging transducer may be in the form of a sheet, ring, half ring, etc., and in this embodiment, the imaging unit 422 is preferably in the form of a sheet.

Referring to fig. 1 to 11, in one embodiment of the puncture system and the ultrasonic ablation system, compared with the medical apparatus compatible with the puncture and ablation function in the prior art, the puncture (or "puncture" is performed) is performed on the epidermis (or the tracheal wall, the esophageal wall, etc.) of the human body through the conical tip 411, and further the specific target tissue (such as tumor blocking the trachea, lung nodule, liver cancer tumor, etc.) in the human body is punctured, the specific target tissue is isolated from the ablation unit 424 through the connecting tube 43, the ablation unit 424 is prevented from directly contacting the specific target tissue, and the ablation unit 424 generates heat by ultrasonic waves and focuses the heat deep in the specific target tissue, and the temperature at the focal point is the highest, so that the ablation is performed on the specific target tissue by generating enough heat at the focal point, thereby avoiding damage to non-target tissue (such as blood vessels, etc.), and improving the safety. The energy unit comprises an imaging unit 422 and an ablation unit 424, so that the imaging unit 422 images tissues in the coverage area of the energy unit, the position of the puncture system 40 in a human body is observed in real time, the position of a specific target tissue is confirmed through imaging images, and then the ablation unit 424 ablates the specific target tissue, thereby avoiding a doctor from repeatedly observing images of the human body tissue in operation, reducing the operation steps of the doctor, shortening the operation time and reducing the risk of complications of the operation.

Referring to fig. 3 to 6, a puncture system 40 according to the present embodiment comprises: a penetration unit 41, an engagement tube 43 sleeved on a part of the penetration unit 41, and an energy assembly 42 disposed inside the engagement tube 43 and connected to the penetration unit 41; the penetration unit 41 penetrates the epidermis of the human body and the specific target tissue to guide the energy assembly 42 to reach the specific target tissue position, and the specific target tissue is ablated by the energy assembly 42. The puncturing unit 41 includes: a connecting portion 413, an end of the connecting portion 413 remote from the connecting tube 43 extending in the axial direction to form a tapered tip 411 having a tapered outer diameter; the energy assembly 42 includes: a base 420 extending at least partially axially into the connection 413, and an energy unit (not shown) disposed on the base 420, the energy unit including at least an ablation unit 424. Penetration of body tissue is facilitated by the tapered tip 411 to access the interior of the body and further penetrate specific target tissue within the body. The outer diameter of the tapered tip 411 is tapered in a piercing direction so that a piercing hole (not shown) formed in the tapered tip 411 during piercing of the epidermis of the human body and a specific target tissue can be expanded to facilitate the passage of the connection portion 413, the connection tube 43, and the like through the piercing hole. The conical tip 411 pierces the epidermis of the human body to drive the ablation unit 424 to move towards the specific target tissue in the human body to guide the ablation unit 424 to reach the specific target tissue position, the specific target tissue is isolated from the ablation unit 424 by the connecting tube 43, the ablation unit 424 is prevented from directly contacting the specific target tissue, the ablation unit 424 generates heat through ultrasonic waves and focuses the heat deep in the specific target tissue, the temperature at the focus is the highest, and sufficient heat is generated at the focus to ablate the specific target tissue, so that damage to non-target tissues (such as blood vessels and the like) is avoided, and the safety is improved.

Preferably, as shown in fig. 4, the base 420 is recessed radially inward to form a partition portion 425, and the partition portion 425 is provided with an energy unit; the energy unit includes: the imaging unit 422 and the ablation unit 424, the imaging unit 422 and the ablation unit 424 are disposed at two sides of the partition 425 along the circumferential direction. Preferably, the plane T2 of the imaging unit 422 is parallel to the plane T1 of the ablation unit 424. Illustratively, in some embodiments, the plane T2 in which the imaging unit 422 is located forms an angle with the plane T1 in which the ablation unit 424 is located that is greater than 0 ° and less than or equal to 90 °. The conical tip 411 pierces the epidermis of a human body to drive the energy component 42 to move towards a specific target tissue in the human body, and images the tissue in the coverage area of the energy component through the imaging unit 422, so that a doctor can observe the piercing position of the conical tip 411 in the human body in real time in an operation, the piercing direction of the conical tip 411 can be conveniently controlled to pierce the specific target tissue so as to guide the energy component 42 to reach the specific target tissue, the specific target tissue is ablated through the ablation unit 424, the medical instrument used by the doctor in the operation can be reduced through the puncture system 40 with the functions of piercing, imaging and ablating, and the image of the human tissue can be prevented from being repeatedly observed in the operation by the imaging unit 422, so that the operation time is shortened, the non-target tissue can be prevented from being pierced by the conical tip 411, and the risk of complications in the operation is reduced.

Further, the tapered tip 411 is preferably configured as a conical tip to ensure that the tapered tip 411 applies a radially symmetric force to the body tissue when piercing the body tissue, reduce the influence of the body tissue on the piercing direction of the tapered tip 411, improve the collimation of the tapered tip 411 piercing the body tissue, and avoid the tapered tip 411 piercing non-target tissue.

Referring to fig. 6, the conical tip 411 includes a conical surface 412 extending in a direction forming an angle α with the axis P of the conical tip 411 of 2.5 ° or more and 37.5 ° or less. The angle α is preferably 7.5 ° to 12.5 °. The diameter d1 of the tapered tip 411 is 0.5mm or more and 3mm or less, and preferably d1 is 1.5mm or more and 2.5mm or less; the axial length d2 of the tapered tip 411 is preferably 3mm or more and 10mm or less. The inventor experiment proves that the taper tip 411 with the above parameter setting can improve the puncturing effect on human tissues, reduce the puncturing resistance on human tissues, ensure the rigidity of the puncturing unit 41, prevent the puncturing unit 41 from bending in the puncturing process, and avoid the damage of the tissue caused by too strong puncturing force and unsuccessful puncturing caused by too weak puncturing force.

Referring to fig. 3 to 6, the connection portion 413 is configured to accommodate at least a portion of the rotation space 410 of the base 420, and a gap (not shown) is formed between the base 420 and the rotation space 410 for axially rotating the base 420 relative to the connection portion 413. The base 420 is used for driving the imaging unit 422 to rotate around the axis P in fig. 4, so that the imaging unit 422 can image tissues within the coverage range of the imaging unit 422 in the rotating process, the imaging unit 422 is stopped from imaging, the ablation unit 424 is rotated around the axis P by rotating the base 420, the ablation unit 424 is rotated to the position of the imaging unit 422 facing the specific target tissues, and the ablation unit 424 can precisely ablate the specific target tissues, so that damage to non-target tissues is avoided. And excessive ablation can be prevented by rotating the imaging unit 422 to the position of the ablation unit 424 to observe in real time the progress of ablation of the specific target tissue by the ablation unit 424.

Referring to fig. 4 to 6, the imaging unit 422 is disposed at least partially corresponding to the ablation unit 424 in the axial direction. Illustratively, in some embodiments, the imaging unit 422 corresponds to the location of the ablation unit 424 on the bulkhead portion 425 along an axial portion (not shown) such that there is a non-coincident portion of the imaging unit 422 and the ablation unit 424 on the bulkhead portion 425, thereby reducing ultrasound signal interference between the imaging unit 422 and the ablation unit 424; referring to fig. 4, the imaging unit 422 is disposed integrally in correspondence with the ablation unit 424 in the axial direction, and the position of the imaging unit 422 on the partition 425 is covered by the ablation unit 424; to avoid the interference of the ultrasonic signals of the imaging unit 422 and the ablation unit 424 during operation, which are at least partially disposed correspondingly in the axial direction, the spacer portion 425 is optionally configured as a solid plate-like structure, and the spacer portion 425 may be made of a metal material such as copper, silver, or the like, which can isolate the ultrasonic signals; or the side of the baffle part 425, which is attached to the imaging unit 422, and the side of the baffle part 425, which is attached to the ablation unit 424, are respectively provided with isolation layers (421, 423) for isolating ultrasonic signals between the imaging unit 422 and the ablation unit 424, the side of the baffle part 425, which is attached to the imaging unit 422, is provided with the isolation layer 421, the side of the baffle part 425, which is attached to the ablation unit 424, is provided with the isolation layer 423, and ultrasonic signals between the imaging unit 422 and the ablation unit 424 are isolated by the isolation layers (421, 423), so that mutual interference between ultrasonic signals between the imaging unit 422 and the ablation unit 424 is avoided; still further or as shown in fig. 5, the interior of the baffle 425 is configured with a gas filled cavity 426 or a wave absorbing material filled cavity 426 or a vacuum cavity 426 for isolating the ultrasound signals between the imaging unit 422 and the ablation unit 424. The wave absorbing material may be selected from tungsten-containing epoxy resin, etc.

The isolation layers (421, 423) may be made of a metal material, a polymer material, or the like, and preferably a porous structure material having a porosity of 95% or less, and the porous structure material may scatter ultrasonic waves in the porous structure so that energy is offset from each other and a part of the energy is absorbed by the porous structure and converted into heat energy.

Illustratively, in some embodiments, the imaging unit 422 is axially spaced from the ablation unit 424 (not shown). The axial spacing distance between the imaging unit 422 and the ablation unit 424 on the spacer portion 425 may be an integral parameter distance interval contained in the range of 1 cm-5 cm, for example, 1cm, 2cm, 5cm, etc., so as to reduce mutual interference of ultrasonic signals of the imaging unit 422 and the ablation unit 424 in the working process, and the axial spacing distance between the imaging unit 422 and the ablation unit 424 is not easy to be excessively large, otherwise, the accuracy of performing ablation on specific target tissues by the ablation unit 424 is affected.

Based on the specific implementation of the puncture system disclosed in the foregoing embodiment, the application also discloses an ultrasonic ablation system.

Referring to fig. 1-3, an ultrasound ablation system 100 includes: a multilayer catheter 30, a puncture system 40 as disclosed in any of the above embodiments disposed at the distal end of the multilayer catheter 30, a circulation system 20 and a driving system 10 disposed in this order at the end of the multilayer catheter 30 remote from the puncture system 40; the circulatory system 20 communicates with the multilayer catheter 30 to deliver fluid to the puncture system 40, and the drive system 10 drives the base 420 to axially rotate relative to the connection 413. The puncture system 40 punctures human tissue and punctures and advances to the position of a specific target tissue, the energy component 42 images the tissue in the coverage area of the puncture system 40 in the puncture process of the human body, the specific target tissue is ablated, the circulating system 20 injects liquid (preferably physiological saline) into the puncture system 40 through the multi-layer catheter 30 so as to absorb heat generated by the energy component 42, the situation that the heat generated by the energy component 42 directly contacts with non-target tissue to cause damage to the non-target tissue is avoided, the driving system 10 drives the base 420 to axially rotate relative to the connecting part 413 so as to control the stay time of the imaging unit 422 and the ablation unit 424 in the specific target tissue area, the imaging unit 422 images the tissue in the coverage area of the imaging unit so as to confirm the specific target tissue position, the driving system 10 drives the base 420 to rotate so as to drive the ablation unit 424 to rotate around the axis P, the ablation unit 424 rotates to the position of the imaging unit 422 facing the specific target tissue, the specific target tissue is isolated from the ablation unit 424 through the connecting pipe 43, the ablation unit 424 is prevented from directly contacting with the specific target tissue, the non-target tissue is prevented from being damaged, the ablation unit 424 generates heat through ultrasonic waves and focuses on the depth of the specific target tissue, the temperature is high enough to cause the specific target tissue damage (such as to realize the ablation of the specific target tissue is avoided), the ablation is realized, the safety is improved, and the specific target tissue is accurately and the target tissue is prevented from being damaged. The puncture system 40 with the functions of puncture, imaging and ablation is simultaneously arranged in the ultrasonic ablation system 100, so that medical instruments used by a doctor in an operation can be reduced, the imaging unit 422 can prevent the doctor from repeatedly observing images of human tissues in the operation, the operation steps of the doctor are reduced, the operation time is shortened, the conical tip 411 can be prevented from puncturing non-target tissues, and the risk of complications of the operation is reduced.

Referring to fig. 1 and 6 to 9, the multilayer catheter 30 includes: an outer layer catheter 34, an inner layer catheter 31 coaxially arranged in the outer layer catheter 34, and a transmission shaft 36 which axially penetrates the inner layer catheter 31 and is fixedly connected with one end of the base 420 far away from the connecting part 413; the end of the transmission shaft 36 away from the connecting portion 413 extends out of the circulation tank 23 and is connected to the driving system 10, and the driving system 10 drives the transmission shaft 36 to rotate so as to drive the base 420 to axially rotate relative to the connecting portion 413. The base 420 is configured to connect with the connection end 427 of the drive shaft 36, the drive shaft 36 forms a drive end 362 extending into the connection end 427, and the drive end 362 and the connection end 427 may be fixedly connected by bonding or welding, etc., so that the drive system 10 can drive the base 420 to axially rotate relative to the connection portion 413 by driving the rotation of the drive shaft 36, so that the base 420 can adjust the residence time of the imaging unit 422 and the ablation unit 424 in a specific target tissue region.

It should be noted that, the transmission shaft 36 is made of a flexible cable with torque resistance, a wire channel 361 for accommodating the signal wires (4221, 4241) is formed inside the transmission shaft 36, and the imaging unit 422 and the ablation unit 424 are electrically connected through the signal wires (4221, 4241), so as to control the opening and closing of the imaging unit 422 and the ablation unit 424 through an external control device (not shown).

Referring to fig. 1 and 6 to 9, the circulation system 20 includes: the circulation cabin 23 penetrated by the multilayer conduit 30 is formed in the circulation cabin 23 in an axial continuous manner and is communicated with the liquid outlet cavity 231 and the liquid inlet cavity 232 of the multilayer conduit 30, and the liquid outlet pipe 21 and the liquid inlet pipe 22 respectively communicated with the liquid outlet cavity 231 and the liquid inlet cavity 232. Liquid is injected into the liquid inlet cavity 232 through the liquid inlet pipe 22 and is led into the puncture system 40 through the multi-layer catheter 30 to absorb heat generated by the energy component 42, and the liquid with absorbed heat enters the liquid outlet cavity 231 through the multi-layer catheter 30 and finally is discharged through the liquid outlet pipe 21.

Referring to fig. 8 and 9, the liquid inlet cavity 232 is radially inwardly protruded to form a first protrusion 2321, and the liquid outlet cavity 231 is radially inwardly protruded to form a second protrusion 2311; the end of the inner catheter 31 away from the puncture system 40 axially abuts against the first protrusion 2321 to isolate the liquid inlet cavity 232 from the liquid outlet cavity 231, and the end of the outer catheter 34 away from the puncture system 40 axially abuts against the second protrusion 2311. The end of the inner catheter 31 far away from the puncture system 40 is axially abutted against the first convex part 2321 so as to isolate the liquid inlet cavity 232 from the liquid outlet cavity 231 and prevent the liquid in the liquid inlet cavity 232 and the liquid outlet cavity 231 from being mixed. The second protruding portion 2311 is axially abutted by the end of the outer layer catheter 34 remote from the puncture system 40, and the portion of the outer layer catheter 34 extending into the circulation tank 23 is fixedly connected to the circulation tank 23 by means such as bonding, so that the liquid in the liquid outlet chamber 231 is prevented from leaking to the outside of the circulation tank 23.

Referring to fig. 6, 8 and 9, two ends of the connecting tube 43 in the axial direction are respectively sleeved on the connecting portion 413 and the outer catheter 34 and enclose to form a cooling cavity 430 for accommodating the energy component 42; a first channel 32 for liquid circulation is formed between the inner side wall of the inner conduit 31 and the outer side wall of the transmission shaft 36, and the liquid in the liquid inlet cavity 232 flows to the cooling cavity 430 through the first channel 32; a second channel 33 through which liquid flows is formed between the outer side wall of the inner conduit 31 and the inner side wall of the outer conduit 34, and the liquid in the cooling cavity 430 flows to the liquid outlet cavity 231 through the second channel 33. By injecting liquid into the liquid inlet cavity 232 through the liquid inlet pipe 22, the liquid enters the first channel 32 along the direction indicated by the arrow k1 in fig. 8 and flows along the first channel 32 towards the direction of the energy component 42, the liquid enters the cooling cavity 430 along the direction indicated by the arrow Q1 in fig. 6 in the first channel 32 to absorb heat generated by the energy component 42, the liquid absorbing heat in the cooling cavity 430 enters the second channel 33 along the direction indicated by the arrow Q2 in fig. 6 to flow to the liquid outlet cavity 231, and the liquid absorbing heat in the liquid outlet cavity 231 is discharged through the liquid outlet pipe 21 along the direction indicated by the arrow k2 in fig. 9. The circulating flow state of the liquid is maintained through the above process, so that the liquid in the cooling cavity 430 can always have a good cooling effect on the energy assembly 42. The outside of the transmission shaft 36 is provided with a heat shrinkage layer 35, and the transmission shaft 36 is sealed through the heat shrinkage layer 35 to prevent the inside of the transmission shaft 36 from entering liquid.

The outer layer catheter 34 and the inner layer catheter 31 are flexible tubes. When the liquid inlet pipe 22 injects liquid into the liquid inlet cavity 232 for the first time and the liquid flows in the first channel 32, the inner conduit 31 outside the first channel 32 is subject to the pressure of the liquid to expand the pipe diameter in the second channel 33, so that the space of the first channel 32 is increased by using part of the space of the second channel 33, the liquid in the first channel 32 can quickly enter the cooling cavity 430, the energy component 42 is quickly cooled, the damage caused by the excessive temperature of the energy component 42 is prevented, and after the liquid in the first channel 32 enters the cooling cavity 430, the liquid absorbing heat in the cooling cavity 430 enters the second channel 33 again in the direction indicated by an arrow Q2 to flow to the liquid outlet cavity 231, the pressure of the liquid in the inner conduit 31 is reduced, the inner conduit 31 is recovered from the expanded state, the space of the first channel 32 and the space of the second channel 33 are recovered, and the liquid flow of the injection and discharge in the first channel 32 and the second channel 33 are balanced.

As shown in fig. 10 and 11, a guide tube 60 sleeved outside a transmission shaft 36 is arranged between a driving system 10 and a circulating system 20, the transmission shaft 36 rotates axially inside the guide tube 60 and relative to the guide tube 60, a connecting seat 61 for connecting the guide tube 60 is embedded in the tail end of a circulating cabin body 23, the connecting seat 61 is fixedly connected with the circulating cabin body 23 and the guide tube 60, and a dynamic sealing structure is formed at the joint of the transmission shaft 36 and the circulating cabin body 23 so as to prevent liquid in a liquid inlet cavity 232 from leaking in the rotating process of the transmission shaft 36 relative to the circulating cabin body 23; the connection seat 61 is formed between the protruding end 611 in the circulation tank 23 and the circulation tank 23, and a sealing ring 612 is arranged between the protruding end 611 and the circulation tank 23, so that leakage of liquid in the liquid inlet cavity 232 through the connection part of the transmission shaft 36 and the circulation tank 23 can be further prevented by the sealing ring 612.

The above list of detailed descriptions is only specific to practical embodiments of the present utility model, and they are not intended to limit the scope of the present utility model, and all equivalent embodiments or modifications that do not depart from the spirit of the present utility model should be included in the scope of the present utility model.

Furthermore, it should be understood that although the present disclosure describes embodiments, not every embodiment is provided with a separate embodiment, and that this description is provided for clarity only, and that the disclosure is not limited to the embodiments described in detail below, and that the embodiments described in the examples may be combined as appropriate to form other embodiments that will be apparent to those skilled in the art.

Claims (13)

1.A lancing system, comprising:

the device comprises a penetrating unit, a connecting pipe sleeved on part of the penetrating unit, and an energy assembly arranged inside the connecting pipe and connected with the penetrating unit;

The penetration unit includes: a connecting portion extending axially away from one end of the connecting tube to form a tapered tip with a tapered outer diameter;

The energy assembly includes: the energy unit is arranged on the base and at least comprises an ablation unit.

2. The lancing system of claim 1, wherein the extension of the taper contained by the tapered tip is at an angle α of greater than or equal to 2.5 ° and less than or equal to 37.5 ° to the axis of the tapered tip.

3. The lancing system of claim 2, wherein the diameter of the tapered tip is greater than or equal to 0.5mm and less than or equal to 3mm and the axial length of the tapered tip is greater than or equal to 3mm and less than or equal to 10mm.

4. The lancing system of claim 1, wherein the connection is configured to receive at least a portion of a rotational space of the base, the base and the rotational space defining a gap therebetween for axial rotation of the base relative to the connection.

5. The lancing system of claim 1, wherein the base is recessed radially inward to form a barrier portion, the barrier portion providing an energy unit;

The energy unit includes: the imaging unit and the ablation unit are arranged on two sides of the partition plate part in a circumferential direction in an opposite manner;

the plane of the imaging unit is parallel to the plane of the ablation unit, or an included angle formed by the plane of the imaging unit and the plane of the ablation unit is more than 0 degrees and less than or equal to 90 degrees.

6. The lancing system of claim 5, wherein the imaging unit is disposed at least partially axially corresponding to the ablation unit or the imaging unit is disposed axially spaced from the ablation unit.

7. The lancing system of claim 6, wherein the side of the barrier portion that is attached to the imaging unit and the side of the barrier portion that is attached to the ablation unit are each configured with an isolation layer for isolating ultrasound signals between the imaging unit and the ablation unit.

8. The puncture system according to claim 6, wherein the partition portion is configured as a solid plate-like structure, or a cavity configured with gas filled or wave absorbing material filled or a vacuum cavity inside the partition portion to isolate an ultrasonic signal between the imaging unit and the ablation unit.

9. An ultrasound ablation system, comprising: a multilayer catheter, the puncture system according to any one of claims 1 to 8 disposed at the distal end of the multilayer catheter, a circulation system and a drive system disposed in this order at one end of the multilayer catheter remote from the puncture system;

The circulation system is in communication with the multi-layered catheter for delivering fluid to the puncture system, and the drive system drives the base to axially rotate relative to the connection.

10. The ultrasound ablation system according to claim 9, wherein the circulatory system comprises: the circulating cabin body is penetrated by the multilayer conduit, and the circulating cabin body is axially and continuously formed in the circulating cabin body and is communicated with the liquid outlet cavity and the liquid inlet cavity of the multilayer conduit, and the liquid outlet pipe and the liquid inlet pipe are respectively communicated with the liquid outlet cavity and the liquid inlet cavity.

11. The ultrasonic ablation system of claim 10, wherein the multi-layer catheter comprises: the outer layer catheter is coaxially arranged in the inner layer catheter of the outer layer catheter, and the transmission shaft axially penetrates through the inner layer catheter and is fixedly connected with one end, far away from the connecting part, of the base;

One end of the transmission shaft, which is far away from the connecting part, extends out of the circulation cabin body and is connected with the driving system, and the driving system drives the transmission shaft to rotate so as to drive the base to axially rotate relative to the connecting part.

12. The ultrasonic ablation system of claim 11, wherein the inlet lumen is radially inwardly convex to form a first convex portion and the outlet lumen is radially inwardly convex to form a second convex portion;

The inner layer catheter is far away from one end of the puncture system and axially abuts against the first convex part so as to isolate the liquid inlet cavity from the liquid outlet cavity, and the outer layer catheter is far away from one end of the puncture system and axially abuts against the second convex part.

13. The ultrasonic ablation system according to claim 12, wherein two ends of the connecting tube in the axial direction are respectively sleeved on the connecting portion and the outer catheter and enclose to form a cooling cavity for accommodating the energy component;

A first channel for liquid circulation is formed between the inner side wall of the inner layer conduit and the outer side wall of the transmission shaft, and liquid in the liquid inlet cavity flows to the cooling cavity through the first channel;

A second channel for liquid circulation is formed between the outer side wall of the inner layer catheter and the inner side wall of the outer layer catheter, and liquid in the cooling cavity flows to the liquid outlet cavity through the second channel.