CN211327466U

CN211327466U - Injection system with near-end charging function

Info

Publication number: CN211327466U
Application number: CN201922179270.4U
Authority: CN
Inventors: 李彪; 胡晓明; 陈琦; 陈超; 李佳楠
Original assignee: Ningbo Diochange Medical Technology Co Ltd
Current assignee: Ningbo Diochange Medical Technology Co Ltd
Priority date: 2019-12-09
Filing date: 2019-12-09
Publication date: 2020-08-25
Anticipated expiration: 2029-12-09

Abstract

The utility model relates to a reinforced injection system of near-end, including the injection subassembly, piston assembly and feeding device, the injection subassembly include syringe needle and with the syringe of the near-end fixed connection of syringe needle, the inner chamber diameter of syringe needle is greater than the inner chamber diameter of syringe needle, the inner chamber of syringe needle and the inner chamber fluid intercommunication of syringe needle, piston assembly includes force application spare and sets up the piston at force application spare distal end, force application spare can transmit force in the axial, so that the drive piston carries out axial displacement in the inner chamber of syringe needle, realize the sliding seal cooperation with the syringe, feeding device and the inner chamber fluid intercommunication of syringe, feeding device includes the feeding chamber, the interface definition of feeding chamber and the inner chamber of syringe is feeding confluence mouth, feeding confluence mouth is set up the proximal part that is located the syringe. The utility model discloses easily add and inject comparatively thick and thick injection thing, be applicable to minimal access surgery operation and minimal access intervention operation, the injection thing utilizes abundant, injection volume control is accurate, and the security performance is high.

Description

Injection system with near-end charging function

Technical Field

The utility model relates to the technical field of medical equipment, concretely relates to reinforced injection system of near-end.

Background

The origin of the traditional syringe dates back to 15 th century, the traditional syringe is developed to the present, the common specification is from 1 ml to 100 ml, the material is basically fixed to be plastic or glass, and the structure of the syringe is not changed greatly. The design of the traditional injector is aimed at being used for liquid with better fluidity and in vitro injection, but with the recent emergence of new operative types such as minimally invasive surgery, minimally invasive interventional surgery and the like, medical staff puts forward the requirements of injecting injection such as medicine or treatment substances into human bodies by using the injector in the operative types, for example, the injection of filling substances with higher viscosity in tissue repair or tissue filling operation and the injection of the medicine or the filling substances into heart parts through a vascular system in the minimally invasive surgery are applied, and aiming at the new requirements, the traditional injector is still used by the medical staff when patients are treated at present, and the following problems can be caused:

1. when a traditional syringe is used for feeding (namely, adding an injection), a feeding mode of sucking back from the far end of the syringe (namely, an injection needle) is usually adopted, but when the injection is viscous, the flowability is poor, and the aperture of the injection needle is small, so that the requirement on the air tightness of the circumferential edge of a piston after the syringe and the piston of the syringe are matched is extremely high, medical staff requires that the piston can freely and smoothly slide in the syringe so as to easily and quickly realize feeding and subsequent injection operation, the pair of contradictory requirements is hardly met by the medical material design which can be selected by the syringe and the piston and the size matching design of the syringe and the piston, and the traditional syringe is only suitable for adding the non-viscous injection with good flowability. If a traditional syringe is used and the existing charging mode is forcibly adopted to add the viscous injection, the bacteria-containing gas in the external environment can enter the syringe from the tail part of the syringe through the circumferential edge of the piston, so that the injection is contacted and mixed with the bacteria-containing gas to be polluted, the operation safety is greatly reduced or lost, the inhaled quantity of the injection cannot be accurately quantified due to the fact that the mixed air volume cannot be accurately measured, and when the treatment with high requirement on the precision of the injected dose is performed, the aim of accurate treatment cannot be fulfilled, and the treatment effect is influenced. In order to solve the problem, medical staff may adopt a method of pulling out a piston rod and feeding from the tail part of the syringe under the condition of the existing syringe, and the method realizes feeding, but causes the following problems: a) because the piston and the injectate have to be exposed to the external bacteria environment and polluted, the safety of the operation is greatly reduced or lost; b) after the charging is finished, the piston is inserted into the injector again and matched, the phenomenon that the external air is mixed into the injection or the injector can be generally found, the injection is viscous and poor in flowability, so that the mixed air cannot be discharged from an injection needle hole, if the method is adopted for injecting the injection, the safety problems of air embolism and the like in the operation can be caused, the integral performance of the injection can be caused due to the mixed air, the operation effectiveness problems such as the reduction of the mechanical strength of the injection and the like can be caused, and the operation safety and effectiveness problems such as the great prolongation of the time for the injection to finally reach the stable performance can be caused. In summary, conventional syringes are not suitable for adding and injecting viscous injectate with poor flow.

2. The piston head end of a traditional injector is usually designed into a smooth plane or an arc-shaped surface, and a connecting area is arranged at the part of the injector connected with the injection needle, so that when the injector pushes the injection, the problem that the injection cannot be completely pushed out of the injector can occur, and a part of the injection always remains in the connecting area between the injector and the injection needle and in the injection needle hole. The problem can be ignored when the injector injects liquid with better fluidity, but when medical staff injects injection with higher viscosity, the injection blocks a needle hole or blocks a connecting area between the injector and an injection needle, and the like, under the condition, after a piston in the injector pushes the injection towards an injection needle end to a limit position, the injector can only be thrown away and cannot be used again, so that the operation cost is increased to a certain extent; and when medical staff needs to inject a small amount of injection and the injection is expensive, the problem that the traditional injector can not completely push out the injection is caused: a) a part of the injectate always remains in the connecting area between the injector and the injection needle hole, so that the injectate is wasted, and the utilization rate of the injectate cannot be maximized, thereby obviously increasing the operation cost; b) the viscosity of the injection is high, the tissue of a target injection position is compact, and a plurality of adverse factors such as the thinness of a needle hole of the injection needle cause that the hand feeling resistance is large or the injection resistance is small when the piston is pushed in the injection process, so that the use and operation difficulty is high, the injection speed is not uniform, the injection amount of the injection cannot be accurately controlled, and finally, the injection is in operation, especially, the injection is excessive during in vivo injection, so that the injection leaks and other fatal risks, or the injection amount in the operation is insufficient, so that the operation fails due to the fact that effective injection cannot be realized.

3. In minimally invasive surgery or minimally invasive interventional surgery, in order to deliver an injection such as a therapeutic substance to a target tissue or organ in a body, it is necessary to use passages in the body of a human body or an animal, including but not limited to the cardiovascular system in the body, respective natural orifices opened on the body surface, and respective artificial passages. These passages, particularly the cardiovascular system and the respective cavities in the body, have the characteristics of tortuosity, slimness and the like, while the traditional syringe is hard and thick, which can cause the following problems if the traditional syringe is directly passed through the passages for minimally invasive surgery or interventional therapy: a) the syringe on the outer part of the traditional injector, the piston on the inner part and the piston rod cannot be bent along tortuous channels, and further the target tissue or organ cannot be reached through the channels; in particular, when using such a channel of the cardiovascular system in vivo as commonly used in minimally invasive interventional procedures, the conventional syringe (including the injection needle) cannot be percutaneously punctured from the body surface into the carotid artery, the radial artery, the femoral artery and the like to reach organs deep in the body, such as the heart, through tortuous vascular paths, so that the conventional syringe cannot perform (percutaneous) minimally invasive interventional injection treatment on the heart through the autologous vascular system in the body, which naturally includes performing myocardial minimally invasive injection by reaching the left ventricle cavity through the channel of the cardiovascular system; b) the piston of the traditional injector is designed into an integral structure, cannot be bent and deformed, and therefore cannot be bent along a tortuous channel, including the channel such as a conduit sheath which is bent or shaped into a certain specific shape or certain shapes, and the like, in a flexible way, when the piston designed in the way is arranged in an injection tube, and then the injection tube is placed in the tortuous channel, including the channel such as the conduit sheath which is bent or shaped into a certain specific shape or certain shapes and the like, the pushing resistance is huge, or the sliding sealing property after the piston is matched with the injection tube cannot be met, and finally the injection performance of the injector is greatly weakened or even lost; c) the various channels mentioned above are fine, when the target tissue or organ is a heart buried in the body, the medical staff is difficult to observe the specific shape of the surface, which inevitably cannot realize the control of the precision of the injection position; in particular, when using artificial access, such as a small incision through the chest and creating an endoscopic access to the target tissue, and more particularly, when using a (thoracoscopic) approach to access the outer surface of the heart for myocardial minimally invasive injection, the operating space is limited due to the small size of the incision, the small size of the access, etc., and it is difficult for the medical staff to visually observe the distal end of the syringe. In short, the conventional syringe cannot be applied to minimally invasive surgery or minimally invasive interventional surgery to inject an injection material into a focal site deep in a human body.

Therefore, there is a need to design and develop an injection system suitable for minimally invasive surgery and minimally invasive interventional surgery, and used together with a myocardial minimally invasive injection surgery and the like through an in-vivo channel, particularly through an endoscopic channel or an in-vivo cardiovascular system channel.

Disclosure of Invention

In view of this, the utility model aims at providing a follow reinforced injection system of near-end for solve the unable drawback that is applicable to minimal access surgery operation and minimal access intervention operation of current traditional syringe, and when the thick form injection thing of injection, the operation degree of difficulty of using is very big, can't ensure the security and the validity of injection thing and adding the back operation of syringe, the unable accurate control injection volume of injection thing, the problem that the injection thing utilization ratio is low.

The utility model aims at realizing through the following technical scheme:

a proximal-end-charging injection system comprises an injection assembly, a piston assembly and a charging device, wherein the injection assembly comprises an injection needle and an injection tube which is connected with the proximal end of the injection needle in a sealing way, the diameter of the inner cavity of the injection tube is larger than that of the injection needle, the inner cavity of the injection needle is communicated with the inner cavity of the injection tube in a fluid mode, the piston assembly comprises a force application member and a piston arranged at the distal end of the force application member, the force application member is capable of transmitting force in the axial direction, so as to drive the piston to axially move in the inner cavity of the injection tube and realize sliding sealing fit with the injection tube, the charging device is in fluid communication with the inner lumen of the injection tube, the charging device comprising a charging lumen, the interface of the feed cavity and the inner cavity of the injection tube defines a feed junction disposed at a proximal portion of the injection tube.

The purpose of the utility model is further realized by the following technical scheme:

in some embodiments, a one-way valve structure is provided on the charging device.

In some embodiments, an interface is provided on the charging device.

In some embodiments, the force applying member is a rod-like structure or a tubular structure.

In some embodiments, the force applying member is made of a solid material.

In some preferred embodiments, the length of the piston assembly is greater than or equal to the length of the syringe.

In some embodiments, an injection grip is provided at the proximal end of the syringe.

In some preferred embodiments, a grip interface is provided on the injection grip.

In some more preferred embodiments, a detachable connection structure is provided on the grip interface and/or on the interface.

In some more preferred embodiments, the detachable connection structure is one or more of a plug-in matching structure, a thread structure and a buckle structure.

In some embodiments, the syringe, force-applying member and/or needle are made of a solid material that is capable of undergoing flexural deformation without undergoing tensile and compressive deformation.

In some preferred embodiments, the solid material comprises a polymer material having shape-recovery properties, a metal material having shape-memory function and high elastic properties, a wire bundle or cable in which metal or polymer filaments or wires are wound or twisted together in a spiral manner to form a hollow or solid structure.

In some preferred embodiments, the syringe and/or the force applicator are made of a multi-layer composite material commonly used in minimally invasive interventions.

In some embodiments, a fixed bend or an adjustable bend, or a hollow movable stop or articulation structure, is provided at the distal portion of the syringe.

In some embodiments, the injection system is optionally provided with a sheath having a fixed bend angle or a real time adjustable bend, the injection tube and injection needle being disposed within the sheath.

In some embodiments, the piston is made of a polymeric material having elasticity and shape recovery.

In some embodiments, the outer surface of the piston assembly is provided with a coating or layer of a material having a surface coefficient of friction of 0.3 or less.

In some embodiments, the piston assembly is made of a material having a surface coefficient of friction of 0.3 or less.

In some embodiments, the force applying member is a driving device disposed at a proximal end portion of the syringe tube, the driving device is in fluid communication with the lumen of the syringe tube, and the driving device is capable of releasing fluid so as to push the piston to move in a distal direction along the lumen of the syringe tube.

In some preferred embodiments, the fluid comprises heparin saline, physiological saline, contrast fluid, sterile water for injection.

In some preferred embodiments, the force applying member further includes a wire, a proximal end of the wire is connected to a wire retrieving device, the wire retrieving device is located at a proximal end portion of the injection tube, the wire retrieving device includes a rotating shaft and a wire retrieving disc fixedly connected to the rotating shaft, a proximal end of the wire is fixedly connected to the wire retrieving disc, the rotating shaft is rotated to drive the wire retrieving disc to rotate, so that the wire is wound on the wire retrieving disc to drive the piston to move towards the proximal end of the injection tube, a one-way sealing port is provided in a proximal end region of the injection tube, and the one-way sealing port is located between a proximal end of the material feeding merging port and the proximal end of the injection tube.

In some more preferred embodiments, the take-up reel is located in the proximal region of the injection tube, and the rotating shaft passes through the one-way sealing port and is fixedly connected with the take-up reel.

In some preferred embodiments, the force applying member further comprises a wire having a one-way sealing port disposed on a proximal region of the syringe tube, the one-way sealing port being located between the proximal end of the feed junction and the proximal end of the syringe tube, the wire extending through the one-way sealing port and out of the syringe tube.

In some embodiments, the distal portion of the plunger is provided with a plunger tip, the plunger tip is capable of being coaxial with the injection needle, the maximum diameter of the plunger tip is smaller than the diameter of the inner cavity of the injection needle, and the axial length of the plunger tip is slightly greater than or equal to the length of the injection needle, the plunger tip is capable of moving in the inner cavity of the injection needle, so that the injectate in the inner cavity of the injection needle can be pushed out of the injection needle.

In some preferred embodiments, the piston spike is connected to the distal end of the piston.

In some preferred embodiments, the piston thimble is a reducing structure with a diameter gradually reduced from the proximal end to the distal end.

In some preferred embodiments, the piston spike is embedded in the piston and is capable of being pushed or ejected into the injection needle when the piston is pushed to the distal end of the syringe.

In some more preferred embodiments, the piston of the piston assembly and the force applying member are hollow structures capable of fluid communication, the piston spike is disposed within the hollow structure, and a proximal end of the piston spike is disposed outside the piston assembly.

In some preferred embodiments, an ejection mechanism is provided within the piston, and the piston spike is ejected from within the piston into the injection needle by the ejection mechanism.

In some embodiments, a needle tube connecting area is arranged at the joint of the inner cavity of the injection tube and the inner cavity of the injection needle, and the needle tube connecting area is of a reducing structure, and the inner diameter of the reducing structure is gradually reduced from the proximal end to the distal end so as to guide the piston thimble to be inserted into the inner cavity of the injection needle.

In some preferred embodiments, the distal portion of the plunger has a shape that matches the shape of the needle cannula coupling area.

In some embodiments, a visual marker is provided on the syringe, and/or on the injection needle, and/or on the force application member, and/or on the piston spike.

In some preferred embodiments, the visual marker is a marking line.

In some preferred embodiments, the visual marker is made of a material having X-ray developability.

In some preferred embodiments, the visual marker is made of a material having sonographic properties.

In some embodiments, the piston is formed by connecting a plurality of small pistons, and the adjacent small pistons are connected through one or more hinge rings.

Compared with the prior art, the beneficial effects of the utility model are mainly embodied in that:

1. the technical scheme provided by the utility model, the feeding device setting that will add the injection thing is located injection assembly's proximal part for: a) the injection is added from the proximal part of the injection tube, so that the viscous injection is easy to add and inject, and accurate injection can be realized; b) the injection moves in a single direction towards the far end from beginning to end in the feeding process and the subsequent injection process, but the feeding process and the injection process of the traditional injector move back and forth, so that various operation safety and effectiveness problems such as injection property change caused by air mixed into the injection can be avoided, and quantitative control of the injection addition can be accurately realized; the unidirectional movement is forward-push movement, and is not a backward-pull suction manner adopted in the charging process of the traditional injector, so that the charging operation of medical personnel is more labor-saving, the operation hand feeling is improved, the defects of the traditional injector are overcome, and the size matching design requirements of an injection tube and a piston are reduced; d) the system is well suited for adding and injecting the commonly used poorly flowing viscous injectate such as tissue repair or tissue augmentation.

2. The utility model discloses a piston assembly through the setting of piston, application of force spare and application of force portion of gripping for: a) when the force application member is applied by medical staff to move at a certain speed, the force can be timely transmitted to the piston, so that the piston moves at the same speed for an equal distance, and the whole piston assembly together with the injection in the syringe moves in the inner cavity of the syringe completely synchronously, thereby facilitating the accurate control of the injection amount of the injection; b) the system can be used for in vitro injection, and is more suitable for in vivo injection in minimally invasive surgery and minimally invasive intervention operation, in particular to myocardial minimally invasive injection operation carried out by an endoscope way or a cardiovascular system way.

3. The utility model discloses be provided with the piston thimble at the distal end portion of piston, be provided with the needle tubing joining region of throat structure in the junction of the inner chamber of syringe and the inner chamber of syringe needle to and the shape of piston distal end portion matches each other with the shape of needle tubing joining region, these designs finally make the injection that adds in the syringe inner chamber together with the injection of syringe needle inner chamber is discharged from the syringe needle almost completely, improves the injection utilization ratio on the one hand greatly, finally makes the utilization ratio of the injection in the injection subassembly reach the maximize, on the other hand also guarantee powerfully that the injection can not remain in the injection subassembly, avoid blockking up the emergence of syringe needle, naturally, this system can feed in raw material and inject once more, consequently reduce the operation cost.

4. The utility model discloses be provided with visual sign, the medical staff naked eye of being convenient for or observe with the help of means such as medical science development equipment, can not only reach the accuracy control to the injection volume, can also real time monitoring syringe needle pierce the whole process of piercing in the myocardium wall, ensure that the syringe needle pierces the degree of depth ideal, finally make the operation process have sufficient security.

5. The present invention provides injection assemblies and piston assemblies of various embodiments, for example: the injection tube and the force application part and/or the injection needle are made of solid materials which can be bent but not stretched or compressed, the injection tube and/or the force application part are made of multi-layer composite materials commonly used in minimally invasive intervention, a fixed bending section or an adjustable bending section is arranged at the distal end part of the injection tube, or a hollow movable limiting structure or an articulation structure is arranged, the piston is made of high polymer materials with elasticity and shape resilience, a material coating or a coating layer with a surface friction coefficient smaller than 0.3 is arranged on the outer surface of the piston component, the piston component is directly made of materials with a surface friction coefficient smaller than 0.3 or is made of a mixture of materials, the injection system is provided with a sheath tube with a fixed bending angle or can be bent in real time, and the injection tube and the injection needle are arranged in the sheath tube. These designs give good flexibility and dimensional compatibility of the channel access, good torque and axial force transmissibility, good space controllability, so the utility model is very suitable for in vivo injection during minimally invasive surgery and minimally invasive interventional surgery, in particular for myocardial minimally invasive injection surgery performed via an endoscopic approach or via a cardiovascular system approach.

Drawings

Fig. 1a is a schematic structural diagram of a first embodiment of the present invention.

Fig. 1b and fig. 1c are the schematic structural diagrams of the check valve structure provided by the present invention when opening and closing respectively.

Fig. 1d is a schematic structural view of a check valve according to another embodiment of the present invention.

Fig. 1e is a schematic structural diagram of the check valve according to another embodiment of the present invention.

Fig. 1f and fig. 1g are schematic diagrams of detachable connection structures of two embodiments of the interface of the present invention.

Fig. 1h to fig. 1k show the working principle of the present system in the present invention, wherein fig. 1h is a state when an injection is to be added, fig. 1i is a state when an injection is being added, fig. 1j is a state when an injection is to be performed, and fig. 1k is a state when the injection of the injection is completed.

Fig. 2a and 2b are schematic structural diagrams of a second embodiment of the present invention, wherein fig. 2a is a state when an injection is about to be added, and fig. 2b is a state when injection of the injection is completed.

Fig. 3a to 3d are schematic structural views of a third embodiment of the present invention, wherein fig. 3a, 3b and 3c are schematic structural views of three embodiments, respectively, and fig. 3d is a state diagram of fig. 3c when the injection of the injectate is completed.

Fig. 4a and 4b are schematic structural views illustrating a first embodiment of a fourth embodiment of the present invention, wherein fig. 4a is a state in which a distal end of a piston needle is just entering a needle; fig. 4b shows the state of fig. 4a in which the injection of the injectate is completed.

Fig. 4c and 4d are schematic structural views of a second embodiment of a fourth embodiment of the present invention, wherein fig. 4c is a state in which the piston needle is ready to enter the injection needle; fig. 4d shows the final state of the plunger tip of fig. 4c entering the needle cavity.

Fig. 5 is a schematic diagram showing only a distal portion of the system according to a sixth embodiment of the present invention.

Wherein: 1 is an injection component, 2 is a piston component, 3 is a feeding device, 4 is an injection, 5 is a traditional injector sold on the market or a container capable of containing the injection, 6 is a sheath, 11 is an injection needle, 12 is an injection tube, 13 is an injection holding part, 21 is a piston, 22 is a force application part, 23 is a force application holding part, 24 is a driving device, 25 is a marking line, 31 is a feeding cavity, 32 is a feeding converging port, 33 is a one-way valve structure, 121 is a needle tube connecting region, 131 is a holding part interface, 132 is a one-way sealing port, 211 is a piston thimble, 221 is fluid, 222 is a line, 231 is a take-up device, 232 is a rotating shaft, 233 is a take-up reel, 234 is a rotating handle, 311 is an interface, 331 is a pulling-inserting part, 332 is a screwing part, and 333 is a sealing part.

Detailed Description

In order to make the objects, technical solutions and advantages of the present invention more clearly understood, the present invention will be further described in detail with reference to the accompanying drawings and examples.

To more clearly describe the structure of a proximal-loading injection system provided by the present invention, the terms "proximal" and "distal" are defined herein, which terms are conventional in the medical device art. Specifically, "proximal" refers to the end of the surgical procedure that is closer to the operator, and "distal" refers to the end of the surgical procedure that is further from the operator.

The first embodiment is as follows:

as shown in fig. 1a to 1k, the present invention provides a proximal end charging injection system (hereinafter referred to as "the present system"), the present system includes an injection assembly 1, a piston assembly 2 and a charging device 3, the injection assembly 1 includes an injection needle 11 and an injection tube 12 hermetically connected to a proximal end of the injection needle 11, a diameter of an inner cavity of the injection tube 12 is larger than a diameter of an inner cavity of the injection needle 11, the inner cavity of the injection needle 11 of the injection assembly 1 is in fluid communication with the inner cavity of the injection tube 12, the piston assembly 2 includes a force applying member 22 and a piston 21 disposed at a distal end of the force applying member 22, the force applying member 22 can transmit force in an axial direction so as to drive the piston 21 to axially move in the inner cavity of the injection tube 12 along an inner cavity central axis m of the injection tube 12, so as to achieve a sliding sealing fit with the injection tube 12, in one embodiment, an injection grip 13 is provided at the proximal end of the syringe 12, and these designs facilitate the subsequent medical personnel to operate the system, for example, keeping the position of the injection grip 13 unchanged, and simultaneously moving all injectate that has been added to the lumen of the syringe 12 in the distal direction while pushing the entire plunger assembly 2 in the distal direction. In the present embodiment, the force applying member 22 has excellent force transmission characteristics when being subjected to a tensile force in the axial direction and when being subjected to a compressive force, for this purpose, the force applying member 22 should be made of a solid material, and formed into any one or more shapes, such as a rod, a tube, etc., preferably, the force applying member 22 is a rod-shaped structure (rod) or a tube-shaped structure (tube) and is matched with the inner cavity of the syringe 12, and in view of the advantage of the solid material having a constant volume, the force applying member 22 will not be axially stretched and compressively deformed, so that the design is convenient for medical staff to obtain a certain pushing force when operating the proximal end region of the force applying member 22 or the later-mentioned force applying grip 23 connected to the proximal end of the force applying member 22 to apply the force applying member 22 so that the force applying member 22 moves a certain distance at a certain speed, and the distal piston 21 can very timely obtain the pushing force and move an equivalent distance at the same speed, thereby ensuring that the entire piston assembly 2 moves in the interior of the syringe 12 in a perfectly synchronized manner, thereby facilitating accurate control of the volume of injectate injected. In one embodiment, a force applying grip 23 is attached to the proximal end of the force applying member 22 to enhance the comfort of the medical professional's hand feeling when manipulating the plunger assembly 2, as shown in FIG. 1 a.

In the direction of the central axis m, the length of the piston assembly 2 should be greater than or equal to the length of the syringe 12, which ensures that when the piston 21 moves to the limit towards the distal end in the inner cavity of the syringe 12, the distal end of the piston 21 can abut against the proximal end region of the injection needle 11, as shown in fig. 1k, so that the subsequently mentioned injectate introduced into the inner cavity of the syringe 12 can be almost completely expelled from the syringe 12, and the injectate utilization rate is finally improved; at the same time, since the force applying member 22 is not compressed and deformed when being axially pressed, at least a portion of the force applying member 22 can be kept outside the injection assembly 1 so that the medical staff can touch or directly operate the portion, and besides, since the force applying member 22 is not subjected to tensile deformation when being axially subjected to tensile force, when the medical staff operates the piston assembly 2, for example, when the proximal end region of the force application member 22 or the force application grip portion 23 is operated to apply a certain pulling force to the force application member 22, the pulling force can be transmitted to the piston 21 in time, thereby ensuring that the retraction movement of the whole piston assembly 2 is synchronous, so as to shorten the time required for the piston assembly 2 to be retracted to the initial position when charging, and finally increase the feasibility of the system for minimally invasive surgery and minimally invasive intervention operation and repeated use when multiple injections are required in extracorporeal injection.

The syringe 12 and the force applying member 22 in the present system are made of a solid material that can undergo bending deformation but not tensile and compressive deformation to provide sufficient bending adaptability, torque transferability and axial force transferability, so that the syringe and the force applying member of the present system have an axial length of at least several hundred millimeters and a maximum dimension of an outer diameter of not more than 5mm, and have excellent bending adaptability and dimensional compatibility for access to a channel to accommodate an endoscopic internal channel and a tortuous cardiovascular system in vivo, ensuring effective access to a focal site. In addition, the system can perform a plurality of times of circumferential rotation around the central axis of the system and swing in the endoscope or the wound protector in the operation process, so that a plurality of times of targeted injections of several to tens of points are performed in the free wall area of the left ventricle of the heart, and the excellent torsion transmissibility and axial force transmissibility of the system enable the system to have good space controllability (including controllability such as positioning of a three-dimensional space) and are convenient to use in minimally invasive cardiac surgery or minimally invasive interventional surgery.

In one embodiment, the solid material is a flexible material or an elastic material, including a polymer material with shape recovery, such as silica gel, rubber, silicone rubber, polyurethane, polyether block amide, polyolefin elastomer, a metal material with shape memory function and high elasticity, such as nickel titanium alloy, cobalt chromium alloy, and a wire or a cable formed by winding or twisting metal or polymer wires or wires in a spiral manner to form a hollow or solid structure, on the basis of which the injection needle 11 is preferably made of a solid material that can be bent without being stretched or compressed; in another embodiment, the injection tube 12 (and/or the force applying member 22) is made of a plurality of medical materials commonly used in minimally invasive medical interventions by a certain connection process to form a multi-layer composite material (e.g., a three-layer composite tube with a woven mesh tube as an intermediate layer, a three-layer composite tube with a coil spring tube as an intermediate layer, etc.), and in a third embodiment, a fixed bent section or an adjustable bent section is disposed at a distal end portion of the injection tube 12, and a hollow movable limiting structure or an articulation structure may also be disposed. As shown in fig. 5, the system can also be provided with a sheath tube 6 with a fixed bend angle or a real-time adjustable bend, and the injection tube 12 and the injection needle 11 are arranged in the sheath tube 6. For the piston assembly 2, the piston 21 is made of a polymer material having elasticity and shape recovery, such as silicone rubber, silicone rubber, polyurethane, polyether block amide, polyolefin elastomer, etc., and in one embodiment, the piston 21 and the force applying member 22 are made of a material having a surface friction coefficient of 0.3 or less, including but not limited to Polytetrafluoroethylene (PTFE), Fluorinated Ethylene Propylene (FEP), High Density Polyethylene (HDPE), Ultra High Molecular Weight Polyethylene (UHMWPE); in another preferred embodiment, the force applying member 22 and the outer surface of the piston 21 are provided with a coating or layer of a material having a surface friction coefficient of 0.3 or less, which can significantly reduce the friction between the outer surface of the piston assembly 2 and the inner cavity of the syringe 12, thereby improving the operational feeling of the system, and the system is low in manufacturing cost, and does not affect the material selection of the piston assembly 2 and the syringe 12, so that the system is very suitable for injecting injectate with high viscosity or performing in vivo injection with long injection stroke and injection path tortuosity, such as cardiovascular system.

The loading unit 3 is in fluid communication with the inner lumen of the injection tube 12, the loading unit 3 comprises a loading chamber 31, the interface between the loading chamber 31 and the inner lumen of the injection tube 12 defines a loading junction 32, the loading junction 32 is arranged at the proximal portion of the injection tube 12, specifically, during loading (i.e. adding injectate) of the injection tube 12 through the loading chamber 31, part (as shown in fig. 1 h) or all (as shown in fig. 1a and 1 e) of the piston 21 is always located at the proximal region of the loading junction 32, so that the injection needle 11 of the injection assembly 1 and the injection tube 12 located at the distal region of the loading junction 31 are in fluid communication with the loading chamber 31, and thus injectate enters from the loading chamber 31, enters the inner lumen of the injection tube 12 (as shown in fig. 1 i) through the loading junction 32, And a moderate increase of the amount of the injectate makes it possible to enter the needle lumen of the injection needle 11 and finally to exit from the distal tip of the injection needle 11 (see fig. 1 j).

In one embodiment, as shown in fig. 1a to 1e, the charging chamber 31 of the charging device 3 is provided with a one-way valve structure 33, and the opening and closing of the one-way valve structure 33 can be controlled when the one-way valves of the one-way valve structure 33 are respectively oriented in two different directions, and in a preferred embodiment, the one-way valve structure 33 has an opening state and a closing state which are manually controlled by switches, as shown in fig. 1b and 1c, respectively, and the above-mentioned structure is advantageous in that an operator can grasp the opening and closing of the one-way valve structure 33 at any time, and prevent injectate which has been added to the charging device 3 and the injection assembly 1 from leaking out of the charging chamber 31 during subsequent injection, specifically, when medical personnel need to add injectate to the present system, the one-way valve structure 33 is opened, as shown in fig. 1h, the injectate can smoothly flow into the inner cavity of the injection tube 12 through the feeding cavity 31 to achieve feeding, as shown in fig. 1i, when the feeding process is finished, the one-way valve structure 33 is closed, the force applying member 22 will drive the piston 21 to axially move in the inner cavity of the injection tube 12 in the distal direction along the inner cavity central axis m of the injection tube 12, because the piston 21 is in sliding sealing fit with the inner cavity of the injection tube 12, all the injectate in the inner cavity of the injection tube 12 and at the distal end region of the piston 21 will move in the distal direction, and because the one-way valve structure 33 is in the closed state, the piston assembly 2 can always prevent the injectate in the injection tube 12 from flowing back into the feeding device 3 during the whole moving process, thereby ensuring the injectate to enter from the feeding cavity 31, this is achieved by the final ejection from the distal tip of the needle 11. In summary, the plunger 21 allows both single and repeated charges to be easily and quickly administered from the proximal portion of the syringe assembly 1 via the administration device 3 without the need for withdrawing the plunger rod to administer the charge from the rear of the syringe as described in the background section; the injection material moves in a single direction towards the far end direction from beginning to end in the charging process and the subsequent injection process, so that the problems of performance change of the injection material and the like caused by air mixed into the injection material are avoided, the safety and the effectiveness of the operation are ensured, and the quantitative control of the addition of the injection material can be accurately realized; the unidirectional movement is forward-push movement, and is not a backward-pull suction manner adopted in the charging process of the traditional injector, so that the medical staff is more labor-saving to operate, the operation hand feeling is improved, various defects existing in the adding process of viscous injection materials by the traditional injector are overcome, and the size matching design requirements of the injection tube and the piston are reduced, therefore, the system is very suitable for adding and injecting the viscous injection materials with poor fluidity in tissue repair or tissue filling and the like. In another preferred embodiment, the check valve structure 33 is an automatically openable and closable check valve, for example, a duckbill valve disposed toward the feeding junction 32 as shown in fig. 1d, which not only can make the duckbill of the check valve always open during the feeding process for smooth feeding, but also can make the duckbill of the check valve close once the piston 21 moves in the distal direction during the injection process at any time, so as to ensure that all the injectate in the inner cavity of the injection tube 12 located at the distal region of the piston 21 moves in the distal direction, thereby automatically realizing the opening and closing functions of the check valve according to the usage state of the device. As shown in fig. 1 e.

In an embodiment, the feeding cavity 31 of the feeding device 3 is further provided with a connector 311, the connector 311 is provided with one or more of a quick detachable connection structure such as a plug port (as shown in fig. 1 f), a thread (as shown in fig. 1 g), a snap structure, and the like, so that the feeding device 3 can be detachably connected with the one-way valve structure 33, or the feeding device 3 can be detachably connected with the container 5 which contains the injection. The quick detachable structure shown in fig. 1f is a plug-in detachable structure, the interface 311 is tightly connected with a plug-in member 331 arranged on the one-way valve structure 33 and matched with the interface, so as to ensure that the injectate does not seep out at the position; the quick release mechanism shown in fig. 1g is a screw-type release mechanism, and a surface of the end of the interface 311 far away from the syringe 12 is provided with a screw thread, which is detachably connected with a tightening member 332 provided on the one-way valve mechanism 33, so that in a tightened state, the injectate is ensured not to ooze out at the position. In a preferred embodiment, in order to improve the utilization rate of the injectate and reduce or avoid the possibility of residual injectate in the charging device 3 as much as possible, a plug member 333 connected with the one-way valve structure 33 or the container 5 already containing the injectate can be further arranged on the one-way valve structure 33 or the container 5 already containing the injectate, when the one-way valve structure 33 or the container 5 already containing the injectate is connected with the interface 311 of the charging device 3, the plug member 333 can enter the cavity of the charging cavity 31 and form a matching connection, as shown in fig. 1h, and preferably, the outline of the plug member 333 forms a seamless matching connection with the cavity outline of the charging cavity 31.

As shown in fig. 1h to fig. 1k, when the injectate for addition and injection of the system is viscous, the working principle of the system is as follows:

1. in the step of preparing the loading, i.e. adding injectate, in vitro, it is ensured that part or all of the piston 21 is always located in the proximal region of the loading junction 32, so that the lumen of the injection needle 11 of the injection assembly 1 and the lumen of the injection tube 12 in the distal region of the loading junction 31 are in fluid communication with the loading lumen 31 of the loading means 3 via the loading junction 32, as indicated by the arrows in fig. 1 h.

2. As shown in fig. 1i, a container 5 (such as a commercially available common injector) containing the injectate is connected through the one-way valve structure 33, the one-way valve structure 33 is confirmed to be in an open state, the injectate 4 is loaded through the feeding cavity 31, and the injectate 4 enters the inner cavity of the injection tube 12 through the feeding junction 32; the amount of injectate 4 added to the lumen of the syringe 12 depends on clinical needs.

3. As shown in fig. 1j, the one-way valve structure 33 is closed, if necessary, the piston 21 is slowly pushed along the proximal end of the syringe 12 to the distal end until the injectate 4 flows out of the system at the distal tip of the injection needle 11, so that the air in the lumen of the syringe 12 is completely discharged out of the system.

4. When the system is used for minimally invasive surgery or minimally invasive intervention, the injection needle 11 is positioned and penetrated into a target lesion site along a specific approach path, the position of the injection holding part 13 is kept unchanged, the piston holding part 23 is operated to push the whole piston assembly 2 to enable the piston 21 to move a specific distance along the inner cavity of the injection tube 12 at a certain speed, and medical staff can determine whether the amount of the injection 4 ejected from the distal needle point of the injection needle 11 meets clinical requirements or not by means of volume scale marks and the like arranged on the force application member 22 mentioned in the following embodiments, and of course, the injection 4 can be almost completely pushed out of the injection tube 12 according to clinical requirements, as shown in fig. 1k, namely, one charging and injecting is completed.

Example two:

the embodiment is more suitable for minimally invasive surgery and minimally invasive intervention operation, in particular for minimally invasive intervention operation through a cardiovascular system or through a natural cavity.

Referring to fig. 2a and 2b, the difference between the first embodiment and the second embodiment is that the force applying member 22 is a driving device 24 disposed at the proximal end portion of the syringe 12, the driving device 24 is in fluid communication with the inner cavity of the syringe 12, and the driving device 24 can release the fluid 221 so as to push the piston 21 to move in the distal direction along the inner cavity of the syringe 12. Preferably, for ease of assembly and quick connection, a grip interface 131 may be provided on injection grip 13 for detachable connection with the drive device 24. The distal end portion of the injection tube 12 is provided with a fixed bending section or an adjustable bending section, or a hollow movable limiting structure or an articulation structure, so that the system has outstanding space controllability (including controllability such as positioning of a three-dimensional space).

The present embodiment differs from the first embodiment in the medium for transmitting the force in the axial direction, in particular, the drive means 24 as a power source generates or provides a force which is transmitted indirectly via the fluid 221 to the piston 21 such that the piston 21 can move in the lumen of the syringe tube 12 in the distal direction (and in the proximal direction). Preferably, the fluid 221 may be selected from liquids commonly used in interventional procedures, such as heparin saline, physiological saline, contrast solution, and sterile water for injection, and may also be selected from gases, such as various inert gases, oxygen, and air, and the use of a fluid containing liquid or gas as the fluid 221 has more outstanding advantages compared with the first embodiment, including: a) in the process of minimally invasive interventional surgery through a cardiovascular system or through a natural orifice, when a rod body or a pipe body is used as a force application part 22 and an injection system passes through a blood vessel section or a natural orifice which is bent and circuitous in a body, the injection tube 12 and the force application part 22 are simultaneously in a bent state to push the piston assembly 2, particularly the force application part 22, is bound to touch the inner wall of the injection tube 12, so that the injection tube 12 and the force application part 22 generate large friction, the pushing resistance is large if the pushing resistance is light, the operation handfeel of the system is affected, the piston assembly 2 cannot move in the injection tube 12 if the pushing resistance is heavy, and the injection process cannot be realized, however, the occurrence of the situation can be avoided if the embodiment is adopted, and the resistance of force transmission is greatly reduced; b) the defects that the traditional injector in a charging state causes most of the piston assembly 2 of the system to be exposed out of the injection assembly 1 and kept outside in a straight state, so that the total length of the system needs to be extended by nearly one time, thus requiring a larger operation space and being inconvenient for medical staff to operate conveniently and the like are overcome; c) more importantly, the fluid has no rigidity, and can be used for remarkably adapting and bending or matching a comparatively tortuous channel in a body, such as a vascular system, and reducing mechanical damage caused by friction on the inner wall of a blood vessel or channel wall tissue of a human body, and the advantages are all satisfied with the requirements of minimally invasive intervention operation. In order to maximize the efficiency of the fluid 221 in transmitting pushing or pulling force, the area of the syringe 12 located at the proximal end of the piston 21 and the portion of the driving device 24 containing the fluid 221 should be sealed.

Example three:

the embodiment can be suitable for minimally invasive surgery and minimally invasive intervention operation, in particular to the minimally invasive intervention operation through a cardiovascular system or through a natural cavity.

Based on the second embodiment, as shown in fig. 3a to 3d, the third embodiment differs from the second embodiment in that the force applying member 22 further comprises a wire 222, a one-way sealing port 132 is provided on the proximal end region of the injection tube 12, and the one-way sealing port 132 is located between the proximal end of the charge merging port 32 and the proximal end of the injection tube 12.

In a first embodiment, as shown in fig. 3a, the proximal end of the wire 222 is connected to a wire retrieving device 231 located at the proximal end portion of the injection tube 12, the wire retrieving device 231 includes a rotating shaft 232 and a wire retrieving plate 233 fixedly connected to the rotating shaft 232, the proximal end of the wire 222 is fixedly connected to the wire retrieving plate 233, and rotating the rotating shaft 232 can drive the wire retrieving plate 233 to rotate, so that the wire 222 is wound on the wire retrieving plate 233, and further drive the piston 21 to move towards the proximal end of the injection tube 12, which is beneficial for medical staff to easily operate the wire retrieving device 231, such as a rotating handle 234 disposed outside the system and fixedly connected to the rotating shaft 232, so that the piston 21 can move towards the proximal end of the injection tube 12 more rapidly, so as to shorten the time required for withdrawing the piston 21 to the initial charging position or for resetting, and further enhance the use of the system in minimally invasive surgery, and the feasibility of repeated use when multiple injections are needed in-vitro injection, and the surgical risk to a patient when multiple injections are needed is reduced.

Before or during the charging process of the system by the medical professional, the plunger 21 should be positioned between the charging junction 32 and the proximal end of the syringe tube 12, and the wire 222 can be bent or folded due to the flexible nature of the wire 222. Preferably, in the present system, the length of the bent or folded wire 222 is greater than or equal to the axial length between the proximal end of the feeding junction 32 and the distal end of the injection tube 12, so that when the piston 21 moves to the far end in the inner cavity of the injection tube 12, the distal end of the piston 21 can abut against the proximal region of the injection needle 11 without being affected by the length of the wire 222, so that the entire injection 4 fed into the inner cavity of the injection tube 12 can be discharged from the injection tube 12 to the maximum extent, even to approximately 100%, and finally the utilization rate of the injection 4 is improved. In order to maximize the efficiency of the fluid 221 in transmitting thrust during the injection and discharge of the injectate 4 from the inner cavity of the syringe 12, the take-up reel 233 should be located in the proximal region of the syringe 12, as shown in fig. 3 a; meanwhile, the space in the system that is in fluid communication with the driving device 24 should be sealed, and naturally, the rotating shaft 232 passes through the one-way sealing port 132 (not shown in fig. 3 a) and is fixedly connected with the take-up reel 233, and the rotating shaft 232 and the one-way sealing port 132 should form effective sealing after being matched.

In the second embodiment, the one-way sealing port 132 is located on the injection holding portion 13, the one-way valve structure 33 with the aforementioned functional design is selectively disposed in the one-way sealing port 132, the one-way valve structure 33 is fixedly connected to the one-way sealing port 132, and the wire 222 extends out of the injection tube 12 through the one-way valve structure 33 in the one-way sealing port 132, as shown in fig. 3b, the wire 222 and the one-way valve structure 33 can realize a sliding sealing fit, and this design structure is relatively simple and easy to assemble, and can also exert the effects of the first embodiment. Preferably, a force applying grip 23 is attached to the proximal end of the wire 222, so that the medical staff member can move the plunger 21 towards the proximal end of the syringe 12 after the injection is completed by pulling back the force applying grip 23, so as to finally complete the reset after the plunger 21 is retracted to the position of the initial charging, thereby facilitating the charging and injection again or more times.

In the third embodiment, the one-way sealing port 132 is located at the proximal end region of the injection holding portion 13, and particularly, the one-way sealing port 132 may be located at a holding portion interface 131 provided on the injection holding portion 13, and it is particularly worth mentioning that, in the case that the wire 222 is particularly flexible and easy to deform, and the wire diameter is small, the wire 222 is placed between the driving device 24 and the holding portion interface 131, and the driving device 24 and the holding portion interface 131 are directly detachably connected, as shown in fig. 3c and fig. 3d, which is simpler in design, and certainly, the above-mentioned effect of separately providing the one-way sealing port 132 to achieve sealing can also be achieved.

Example four:

based on the first embodiment, the first difference between the fourth embodiment and the first embodiment is: the distal end portion of the piston 21 is provided with a piston needle 211, the piston needle 211 can be coaxial with the injection needle 11, the maximum diameter of the piston needle 211 is smaller than the inner cavity diameter of the injection needle 11, and the axial length of the piston needle 211 is slightly larger than or equal to the length of the injection needle 11. The plunger 211 can move in the inner cavity of the injection needle 11, so that the injectate in the inner cavity of the injection needle 11 can be pushed out of the injection needle 11 to the maximum extent, even to approximately 100%.

In one embodiment, the piston needle 211 is connected to the distal end of the piston 21, as shown in fig. 1h to 2b and fig. 3b to 4b, which is not only simple in structure, but also facilitates the complete synchronization of the piston needle 211 with the movement of the piston assembly 2 in the injection assembly 1, so that when the piston 21 moves to the far end in the inner cavity of the syringe 12 to the limit, the distal end of the piston 21 abuts against the proximal end of the injection needle 11, so that the injectate in the inner cavity of the syringe 12 and the injectate in the inner cavity of the injection needle 11 are almost completely discharged from the injection needle, and finally, the utilization rate of the injectate in the injection assembly 1 is improved to the maximum, even approaching 100%. Preferably, piston spike 211 is of a gradual size or shape design, and in particular, the diameter of piston spike 211 gradually decreases from the proximal end to the distal end to form a truncated cone or cone shape, as shown in fig. 4a and 4b, which is particularly suitable for injecting highly viscous injectate, and particularly when the injectate also has the property of self-gelling or self-curing, the injectate will soon become semi-fluid or gel, in which case the area of the distal surface or distal apex of piston spike 211 is much smaller than the diameter of the lumen of needle 11 due to the smaller size of the distal-most end of piston spike 211, so that a) the distal end of piston spike 211 keeps the lumen of needle 11 at the moment of entering the needle 11 and during the continuous movement of the needle 11 in the distal direction, as shown in fig. 4a, and the lumen of needle tube 12, i.e., subsequently mentioned needle connecting region 121, continuously keeps with the lumen of needle 11 The fluid communication is maintained, as shown by the arrows in fig. 4a, so that the injectate 4 in the lumen of the syringe 12, i.e., in the subsequently-mentioned syringe connecting region 121, can still be expelled by injection, and therefore the utilization rate of the injectate in the syringe 12 and the subsequently-mentioned syringe connecting region 121 is improved to the maximum, even to approximately 100%; b) the pressure on the far end surface or the far end vertex of the piston thimble 211 is larger, so that the hand feeling resistance of the advancing piston assembly 2 can be obviously reduced, and the operability of the system is enhanced; c) when the piston 21 is pushed to the distal end of the injection tube 12, as shown in fig. 4b, the injectate remaining in the injection needle 11 even after partial solidification can be pushed out of the system mostly, so that the utilization rate of the injectate can be improved to a certain extent, and the injectate is ensured not to remain in the injection needle 11 to cause the blockage of the needle hole, and naturally, the system can carry out feeding and injection again or for multiple times, thereby reducing the operation cost.

In one embodiment, piston needle 211 is embedded in piston 21, and when piston 21 is pushed to the distal end of syringe 12, piston needle 211 can be pushed or ejected into needle 11. In a preferred embodiment, as shown in fig. 4c and 4d, the piston 21 and the force applying member 22 of the piston assembly 2 are hollow structures capable of fluid communication, the piston needle 211 is disposed in the hollow structure and can form a sliding sealing fit with the hollow structure, the length of the piston needle 211 is slightly greater than or equal to the sum of the length of the piston assembly 2 and the length of the injection needle 11, so that the proximal end of the piston needle 211 can extend out of the piston assembly 2 of the system, and more preferably, a piston needle handle is fixedly connected to the proximal end of the piston needle 211, and these designs are convenient for medical staff to operate the piston needle handle to move the piston needle 211 further towards the distal end when the piston 21 is pushed to the distal end of the injection tube 12, so that the injectate 4 remained in the injection needle 11 is almost completely expelled, ensuring that the utilization of the injectate 4 within the injection assembly 1 is maximized, even approaching 100%; of course, at any time when the piston 21 is not pushed to the proximal end of the injection tube 12, the medical staff can operate the piston thimble handle alone to clean the injectate 4 retained in the injection needle 11 at any time, so as to keep the cavity of the injection needle 11 unobstructed, and further ensure the smooth feeding process and the injection process, thereby being convenient for feeding and injecting again or repeatedly by using the system. In another preferred embodiment, the piston needle 211 is embedded in the piston 21, and an ejection mechanism is disposed in the piston 21, and the ejection mechanism can eject the piston needle 211 from the piston 21 by touch sensing or pressure sensing, so that the piston needle 211 can be ejected into the injection needle 11 when the piston 21 is pushed to the distal end of the injection tube 12.

As mentioned above, the diameter of the lumen of the injection tube 12 is larger than the diameter of the lumen of the injection needle 11, when the injection system is used in minimally invasive surgery and minimally invasive intervention, the injection system will undergo a curved shape change to match a comparatively tortuous path in the body, such as the cardiovascular system, this would certainly cause the distal end of the piston spike 211 to be misaligned with the lumen of the needle 11, as shown in fig. 5, it is difficult for the piston spike 211 to enter the inner cavity of the injection needle 11, in contrast, a needle tube connection area 121 is provided at the connection between the lumen of the injection tube 12 and the lumen of the injection needle 11, said needle tube connecting section 121 has a tapered structure whose inner diameter is gradually reduced from the proximal end to the distal end, so as to guide said piston needle 211 to be completely inserted into said cavity of said injection needle 11, and simultaneously, the process that the piston thimble 211 moves from the inner cavity of the injection tube 12 to the inner cavity of the injection needle 11 is ensured to be smooth and smooth.

A second difference is that the shape of the distal part of the plunger 21 and the shape of the lumen of the needle 11 and the distal connecting part of the syringe 12 match each other, as shown in fig. 1e, fig. 1h to 4 d. This design avoids the disadvantages of conventional syringe designs, particularly where the head end of the plunger 21 (i.e., the distal end of the plunger 21 in the present invention) is generally designed to be smooth, flat or arcuate, and the part of the injector connected with the injection needle is also provided with a connecting area, so that when the injector pushes the injection, there occurs a problem that the injectate cannot be completely pushed out of the syringe, so that a part of the injectate always remains at the connection area between the syringe and the injection needle, and when medical staff injects the injection with higher viscosity, the injection can be blocked at the connecting area of the injector and the injection needle, the design of the system can ensure that the utilization rate of the injection 4 added into the injection assembly 1 is improved to the maximum, even the utilization rate can be close to 100 percent, and compared with the traditional injector, the operation cost is reduced to a certain extent.

Example five:

in this embodiment, a visual mark is provided on the syringe 12, the injection needle 11, the force applying member 12, the piston 21, or the piston thimble 211 of the present system, and in one embodiment, a marking line 25 indicating a volume scale is provided on the force applying member 12, as shown in fig. 1e, so that a medical staff can directly and visually observe the change of the marking line 25 to precisely control the injection amount 4. In another embodiment, when the system is used for injection in minimally invasive surgery and minimally invasive intervention, in order to facilitate the medical staff to judge the position in the human body and ensure the accuracy of the injection position, the injection needle 11 is provided with a visual mark. Preferably, in order to confirm whether the injection object 4 in the cavity of the injection needle 11 is completely injected, the piston needle 211 may be provided with a visual mark, and when the image of the piston needle 211 on the computer screen is observed to be completely placed in the image of the injection needle 11, the injection object 4 can be judged to be completely discharged from the system by means of a medical developing device connected to the computer screen, such as an X-ray machine, an ultrasonic image diagnostic device, and the like. The visual mark can be made of materials with X-ray or ultrasonic developability, can realize visualization by matching with developing equipment, and materials which can be used for the visual mark comprise metals such as tantalum, platinum, iridium, platinum-iridium alloy, cobalt, chromium, cobalt-chromium alloy, osmium, tungsten, rhodium, gold, palladium, rhenium and the like or compounds such as barium sulfate, bismuth subcarbonate, bismuth oxychloride, zirconium oxide, bismuth oxide, titanium oxide, niobium oxide and the like. In particular, in order to further enhance the real-time monitoring of the entire penetration process of the injection needle 11 into the myocardial wall, ensure that the needle tip of the injection needle 11 is located in the myocardial wall and is not penetrated, and achieve the desired penetration depth, the distal region of the system, including the injection needle 11 and the distal end portion of the injection tube 12, should be made of a material which can be monitored and observed by the ultrasonic image diagnostic equipment, preferably a metal material having a large density difference with myocardial tissue, such as nitinol, cobalt-chromium alloy, platinum-iridium alloy, platinum-tungsten alloy, tantalum, gold, medical 304 stainless steel, 316L stainless steel, etc.

Example six:

in this embodiment, the plunger 21 can be configured in a variety of different shapes, including a sphere, an oblate cylinder as shown in FIG. 1e, an ellipsoid as shown in FIG. 1h, a double sphere as shown in FIG. 3a, and a shape that matches the shape of the interior cavity of the needle attachment region 121 to ensure that the resistance of the plunger 21 to movement within the cavity of the syringe 12 is as low as possible, and that they form an effective sliding seal to allow the injectate 4 contained within the system to be expelled from the needle 11. In one embodiment, the piston 21 may be formed by directly connecting a plurality of pistons, such as a double sphere shown in fig. 3 a; or a plurality of small pistons can be combined and connected, as shown in figure 5, each small piston is connected with one or a plurality of hinge rings, the hinge rings can play the role of universal joints, when the system is applied to minimally invasive surgery and minimally invasive intervention, the syringe 12 will bend to assume the state shown in fig. 5, and the design of the piston 21 is highly adaptable to the bent syringe 12, the sliding seal effectiveness can be ensured while ensuring excellent force transmission performance when the entire piston 21 is subjected to a tensile force in the axial direction and a thrust force, so that the injectate 4 loaded into the system can be smoothly ejected from the injection needle 11, therefore, the injection is very suitable for in vivo injection in minimally invasive surgery and minimally invasive interventional surgery, in particular to myocardial minimally invasive injection surgery carried out by an endoscopic approach or a cardiovascular system approach.

Finally, it should be understood that the above description is only a preferred embodiment of the present invention, and is not intended to limit the present invention, and any modifications, equivalents, improvements, etc. made within the spirit and principles of the present invention should be included within the scope of the present invention.

Claims

1. A proximal-loading injection system, comprising: comprising an injection assembly (1), a piston assembly (2) and a feeding device (3), wherein the injection assembly (1) comprises an injection needle (11) and an injection tube (12) hermetically connected with the near end of the injection needle (11), the inner cavity diameter of the injection tube (12) is larger than that of the injection needle (11), the inner cavity of the injection needle (11) is communicated with the inner cavity of the injection tube (12) in a fluid mode, the piston assembly (2) comprises a force application part (22) and a piston (21) arranged at the far end of the force application part (22), the force application part (22) can transmit force in the axial direction so as to drive the piston (21) to axially move in the inner cavity of the injection tube (12) and realize sliding sealing fit with the injection tube (12), the feeding device (3) is communicated with the inner cavity of the injection tube (12) in a fluid mode, and the feeding device (3) comprises a feeding cavity (31), the interface of the feeding cavity (31) and the inner cavity of the injection tube (12) is defined as a feeding merging opening (32), and the feeding merging opening (32) is arranged at the proximal part of the injection tube (12).

2. The proximal-loading injection system according to claim 1, wherein a one-way valve arrangement (33) is provided on the loading means (3).

3. The proximal-loading injection system of claim 1, wherein the force-applying member (22) is a rod or a tube.

4. The proximal-loading injection system of claim 1, wherein the force-applying member (22) is a drive device (24) disposed at a proximal portion of the syringe (12), the drive device (24) being in fluid communication with the lumen of the syringe (12), the drive device (24) being capable of releasing the fluid (221) so as to urge the piston (21) to move distally along the lumen of the syringe (12).

5. The proximal-loading injection system of claim 4, wherein the force-applying member (22) further comprises a wire (222), the proximal end of the wire (222) is connected with a wire take-up device (231), the wire take-up device (231) is positioned at the proximal part of the injection tube (12), the take-up device (231) comprises a rotating shaft (232) and a take-up reel (233) fixedly connected with the rotating shaft (232), the near end of the wire (222) is fixedly connected with the take-up reel (233), the rotation of the rotating shaft (232) can drive the take-up reel (233) to rotate, so that the wire (222) is wound on the take-up reel (233), thereby driving the piston (21) to move towards the proximal end of the injection tube (12), a one-way sealing port (132) is provided on a proximal end region of the syringe (12), the one-way seal (132) is located between the proximal end of the feed combination port (32) and the proximal end of the syringe (12).

6. The proximal-loading injection system of claim 5, wherein the take-up reel (233) is located in the proximal region of the injection tube (12), and the rotary shaft (232) passes through the one-way sealing port (132) to be fixedly connected with the take-up reel (233).

7. The proximal-end-loading injection system of claim 4, wherein the force-applying member (22) further comprises a wire (222), a one-way sealing port (132) being provided on a proximal region of the injection tube (12), the one-way sealing port (132) being located between a proximal end of the loading junction (32) and a proximal end of the injection tube (12), the wire (222) extending through the one-way sealing port (132) and out of the injection tube (12).

8. The proximal-loading injection system of claim 1, wherein a distal portion of the piston (21) is provided with a piston needle (211), the piston needle (211) is capable of being coaxial with the injection needle (11), a maximum diameter of the piston needle (211) is smaller than a diameter of a lumen of the injection needle (11), and an axial length of the piston needle (211) is greater than or equal to a length of the injection needle (11), the piston needle (211) is capable of moving in the lumen of the injection needle (11) such that injectate in the lumen of the injection needle (11) can be pushed out of the injection needle (11).

9. The proximal-loaded injection system of claim 8, wherein the piston spike (211) is embedded in the piston (21), the piston spike (211) being capable of being pushed or ejected into the injection needle (11) when the piston (21) is pushed to the distal end of the injection tube (12).

10. The proximal-loading injection system of claim 8, wherein a needle tube connecting section (121) is provided at a junction of the inner cavity of the injection tube (12) and the inner cavity of the injection needle (11), the needle tube connecting section (121) having a tapered structure, and an inner diameter of the tapered structure is gradually reduced from a proximal end to a distal end so as to guide the piston spike (211) to be inserted into the inner cavity of the injection needle (11).