KR101322673B1 - Injection needle for injecting stem cells and syringe equipped therewith - Google Patents

Abstract

The present invention relates to an injection needle and a syringe for injecting stem cells into myocardial tissue necrosis due to myocardial infarction or ischemic heart failure disease. The present invention relates to an injection for cell injection in which a needle shaft is wound in a spiral shape. Provide a needle. The needle and syringe according to the present invention can increase stem cell survival rate in necrotic cardiomyocytes by resuming blood flow to the injected stem cells while preventing cell fluids from leaking out of the epicardium after injection into the myocardial tissue.

Description

Injection needle for injecting stem cells and syringe equipped therewith}

The present invention relates to an injection needle and a syringe having the same for injecting cell fluid into organ tissues of an animal including a human, and more particularly, to effectively inject stem cells into myocardial tissue necrosis due to myocardial infarction or ischemic heart failure disease. The present invention relates to a needle and a syringe for restoring microblood flow to increase cell survival.

Myocardial infarction is a condition in which coronary artery occlusion lasts for a certain period of time, resulting in reduced oxygen and nutrient supply to the entire heart or part of it, resulting in necrosis of myocardial cells. Complications of heart failure due to necrosis of cardiomyocytes in myocardial infarction or ischemic heart failure disease often occur. Heart failure complications increase the risk of cardiovascular death, rely on lifelong medication for symptoms such as shortness of breath, and should be hospitalized repeatedly if severe heart failure occurs.

Cardiomyocytes do not regenerate like neurons, so once damaged they are difficult to treat. Necrotic myocardial tissue is replaced with fibrous tissue, which may remain as scars or calcify. In addition, relatively intact cardiomyocytes around them undergo a process of so-called 'remodeling', which thickens and expands.

Cardiac diseases such as myocardial infarction have conventionally been reliant on drug treatment or surgical operation, but recently it is known that stem cells can be differentiated into cardiomyocytes, transplanting stem cells to the infarcted zone of cardiomyocytes Therefore, studies have been actively conducted to differentiate and regenerate into normal cardiomyocytes.

Tomita et al. Demonstrated that cardiac function was improved by transplanting mesenchymal stem cells isolated from rat bone marrow into myocardial infarction model animals (Tomita S, Li RK, Weisel RD.Autologous transplantation of bone marrow cells improve damaged heart function.Circulation. 1999; 100 (19): 247-256).

Kudo et al. Showed that bone marrow-derived stem cells transplanted into necrotic myocardial tissues differentiated into cardiomyocytes and endothelial cells, resulting in reduced size and fibrosis of myocardial infarction (Kudo, M., Wang, Y). ., Wani, MA, Xu, M., Ayub, A., and Ashraf, M. (2003) Implantation of bone marrow stem cells reduces the infarction and fibrosis in ischemic mouse heart. J. Mol. Cell Cardiol . 35, 1113-1119)

At present, studies are being conducted to treat heart failure by implanting various stem cells including bone marrow derived stem cells into the myocardial infarction site, and various clinical trials are being conducted on the therapeutic products using such stem cells. .

Stem cell transplantation for the treatment of myocardial infarction is performed by placing a catheter along the aorta around the necrotic coronary artery using coronary angiography and administering stem cells, and exposing the heart to open heart to the ischemic damaged heart site. A method of directly injecting stem cells using a syringe has been used.

Such cell injection syringes are not significantly different in the general syringe and its structure and form. Conventional injection needles for cell injection are straight-curve.

Freyman et al. Described the infarcted zone after 14 days of infusion in three different methods: pig intravenous (intravenous infusion, IV), intracoronary infusion (IC), and endocardial injection (EC). As a result of the stem cell survival rate, it was not detected at all in IV, and IC was about 6% and EC was about 3% (Freyman T, Polin G, Osman H, Crary J). , Lu M, Cheng L, Palasis M, et al. (2006) A quantitative, randomized study evaluating three methods of mesenchymal stem cell delivery following myocardial infarction.Eur Heart J 27: 1114.1122).

Various studies have reported that the cell survival rate is very low, 1-5% of the total number of cells injected, in the medical field. (Minort WA, Feye D., Van Den Akker F., Stecher D., Chamuleau SA, Sluijter JP, Doevendans PA (2010) Mesenchymal stromal cells to treat cardiovascular disease: strategies to improve survival and therapeutic results.Panminerva Med 52: 27-40). This low survival suggests that effective methods for injecting stem cells into myocardial infarction are not yet well established.

Wold et al. Puncture normal myocardial tissue at an angle by using a straight-curve needle, a modified form that has bent the middle part of a conventional needle by about 45 degrees, and then stem cells into adjacent necrotic myocardial tissue. (Loren E. Wold, Wangde Dai, Joan S. Dow, and Robert A. Kloner (2007) Stem Cell Therapy in the Heart and Vasculature, Methods) in Molecular Medicine , Vol . 139: Vascular Biology Protocols ). In fact, injecting stem cells into necrosed myocardial tissue using conventional cell injection syringes in animal models, it can be seen that a large amount of cell fluid leaks out of the epicardium after injection. As a result, the amount of cells remaining in the myocardial tissue is significantly reduced compared to the amount of cells actually injected.

In addition, even if stem cells remain in the necrotic myocardial tissue, the injected stem cells are isolated in the necrotic tissue, there is a problem that most of the injected stem cells do not survive and die because the blood supply is still insufficient. In addition, in order to supply blood flow to the injected stem cells, if the entire heart wall penetrates vertically or obliquely with a general needle, there is a high risk of bleeding blood flow from the lumen to the epicardium due to high blood pressure in the heart.

Therefore, it is required to develop a new tool and establish a method for effectively injecting stem cells into the myocardial infarction site.

The present invention has been made to solve the above-described problems, stem cells in the myocardial tissue necrosis by preventing blood from being injected into the myocardial tissue leak out of the epicardium, and resuming blood flow circulation to the injected stem cells An object of the present invention is to provide an injection needle, a syringe containing the same, and a method of using the same, which can increase survival rate.

The present invention provides an injection needle for injecting stem cells into organs, particularly heart tissue of the human body. The present invention provides a needle for cell injection, in which the needle shaft is wound in a spiral shape.

The present invention also provides a needle having a plurality of openings formed on the side of the needle shaft.

On the other hand, the present invention provides a needle that the needle shaft is made of a bioabsorbale material (bioabsorbale material), biodegradable in the organ tissue over time.

On the other hand, the present invention is a needle having a spiral shaft of the above; A syringe barrel on which the needle is mounted; Provided is a syringe comprising a plunger inserted into the syringe barrel.

On the other hand, the present invention provides a syringe further provided with a guide body formed with a guide groove for receiving the spiral shaft. In addition, the outer surface of the syringe barrel provides a syringe with a spiral protrusion corresponding to the inner groove of the guide sieve.

When the cell fluid is injected into the heart wall by using the needle according to the present invention, since a fine spiral channel is formed from the endocardium to the outer membrane, the injected cell fluid does not leak out of the epicardium, thereby increasing the cell survival rate.

In addition, the helical microchannels have the effect of preventing or reducing the occurrence of bleeding from the cardiac lumen toward the epicardium.

In addition, the helical microchannel is considerably longer than the vertical channel, so that a large amount of cell fluid is injected into a relatively large area in a single procedure.

On the other hand, the needle using the shaft of the bioabsorbable material increases the duration of the blood flow supply channel to smoothly differentiate stem cells into cardiomyocytes.

1 is an external view of a needle having a spiral shaft as an embodiment of the present invention.
FIG. 2 is a partial cutaway view of the syringe equipped with the needle of FIG. 1. FIG.
Figure 3a to 3d is a view showing a method of using a syringe equipped with a spiral needle of the present invention.
4 is an external view of a needle having a plurality of openings formed on a side of a shaft as an embodiment of the present invention.
5A is an external view of a needle having a bioabsorbable shaft as an embodiment of the present invention, and FIG. 5B illustrates a connection relationship between a shaft and a hub.
Figure 6 is a cross-sectional view of the syringe equipped with the needle of Figure 5a as an embodiment of the present invention.
FIG. 7A is an external view of a needle combined with two shaft members as an embodiment of the present invention, and FIGS. 7B and 7C are cross-sectional views of coupling members between members.
8 is a cross-sectional view of the syringe equipped with the needle of FIG. 7A as an embodiment of the present invention.
FIG. 9 is a cross-sectional view of the infarcted zone (imfarcted zone) to which the needle of FIG. 7A is applied. FIG.
10 is an external view of a needle that can be treated several times as an embodiment of the present invention.
11 is a cross-sectional view of the syringe equipped with the needle of FIG.
Figure 12 (a) is a photograph of a needle with a conventional straight-curve shaft used for cell transplantation, Figure 12 (b) is a photograph of a needle with a spiral shaft according to the present invention to be.
FIG. 13 is a photograph of injecting stem cells into a rat heart in which a heart beat is maintained using a conventional straight curve needle, (a) is an initial photograph of injection, and (b) is a photograph 5 minutes after the procedure .
14 is a photograph of injecting stem cells into a rat heart in which a heart beat is maintained using a spiral needle of the present invention, (a) is an initial photograph of injection, and (b) is a photograph after 3 minutes of procedure. .
Figure 15 is an experimental result confirming the number of stem cells transplanted using the marker factor cy 5.5, (a) shows the expression level according to the number of cells with xenogen equipment, (b) myocardial infarction rat model (rat model) When the cells of 5 × 10 ⁶ were implanted using a straight curve needle and a spiral needle, respectively, the expression result, and (c) shows the color-bar of the xenogen equipment to identify the cell number.
16 is a result of measuring the change in heart function by echocardiography after inducing myocardial infarction by surgically blocking blood flow in the left anterior descending coronary artery of the rat model. , (a) is a result of injecting saline using a conventional straight curve needle, (b) is a human embryonic stem cell (hESC- differentiated into endothelial cells using a conventional straight curve needle) EC), and (c) is the result of injecting human embryonic stem cells (hESC-EC) differentiated into endothelial cells using the spiral needle of the present invention.

The present inventors inject cell fluid into cardiac tissue using a conventional straight needle, and then penetrate to the lumen of the heart and observe that a large amount of cell fluid leaks back into the epicardium and bleeding occurs from the cardiac lumen toward the epicardium. It was confirmed that.

The present inventors deform the conventional linear injection needle into a spiral wound form, and when the needle is spun while rotating the needle, there is no external bleeding, and the injected cell fluid does not leak into the epicardium. It was confirmed that the present invention was completed.

Hereinafter, the present invention will be described in detail with reference to examples.

[ Example  One]

1 is a perspective view of a needle according to an embodiment of the present invention.

FIG. 2 is a partial cutaway view of the syringe equipped with the needle of FIG. 1. FIG.

1 and 2, the needle assembly 10 of the present invention includes a needle shaft 11 and a needle hub 12. In the present invention, the term 'needle shaft' or 'shaft' means a microtube through which cell fluid passes, and is also commonly referred to as an 'injection needle'. Conventionally used shafts are generally straight or partially curved. On the other hand, the shaft 11 of the present invention is characterized in that it has a spirally wound form.

The diameter of the shaft 11 of the present invention is the same as the diameter of a conventional injection needle for cell injection, and preferably has a diameter of 20 to 33 gauge (guage, G). The outer diameter of the 20G needle is about 0.902 mm, 28G is about 0.356 mm, and 33G is about 0.203 mm.

The diameter of the helix formed on the shaft 11 of the present invention varies, but is usually 2 to 15 mm, preferably 3 to 10 mm.

The spiral angle θ of the helical shaft of the present invention preferably has 5 ° to 45 ° (degree), more preferably 10 ° to 20 °.

The proximal portion of the needle shaft is coupled to the needle hub 12. As shown in FIG. 2, the hub 12 is fitted in an opening of an injection barrel 20. Since the present invention is characterized by the structure of the shaft 11, it is also possible to integrate the shaft is directly coupled to the syringe barrel without a separate hub.

The material of the shaft 11 may be a stainless steel that is used for a general purpose in the needle, in addition to a variety of metals, alloy materials can be used.

The distal end of the shaft is shaped like a conventional needle and has an opening 13 formed therein.

3a to 3d show a method of using a syringe equipped with a spiral needle of the present invention.

When the syringe 1 of the present invention is positioned perpendicular to the epicardial membrane and the syringe barrel 20 is slowly rotated, the needle penetrates the heart wall (or cardiac muscle layer) helically while maintaining the spiral angle θ . When the distal end of the needle reaches a predetermined position, the plunger 30 is pushed to first inject the cell fluid (solution including stem cells) in the barrel (see FIG. 3A). Then, the syringe barrel is continually rotated to puncture the cardiac muscle layer a little more spirally, and then the plunger is pushed again to inject the second cell fluid (see FIG. 3B). Repeat the puncture and injection little by little in the same way as described above (see Figure 3c). When the spiral needle penetrates completely through the heart wall to the endocardium, the syringe barrel is rotated backwards to slowly pull the needle out. In the place where the shaft passed after the procedure, a spiral microchannel is formed, and the cell fluid (stem cells) injected along the microchannel is herpes. Blood in the cardiac lumen supplies oxygen and nutrients to cell fluids injected along the microchannels formed in the endocardium, which significantly increases cell viability. That is, the microchannels resume blood flow up to the cell fluid. Stem cells injected into the necrotic heart muscle layer stably differentiate into cardiomyocytes and regenerate myocardial tissue.

Since the microchannels formed according to the method described above have a very long spiral structure from the endocardium to the outer membrane, blood flow in the heart is not bleeding out of the heart, and there is a markedly small amount as compared to penetrating vertically even with a slight bleeding. If necessary, the risk of bleeding can be further reduced by applying an adhesive drug to the needle traces formed on the epicardium. The microchannel formed according to the present invention has the advantage that a large amount of cell solution is injected in one procedure because the channel is very long compared with the conventional method.

[ Example  2]

4 is a perspective view of a needle according to another embodiment of the present invention.

In the needle 10a of the present embodiment, a plurality of openings 14 are formed on the side of the shaft 11a. The number and location of these openings can be appropriately designed according to the situation such as the diameter of the shaft, the diameter of the spiral. 4 shows a shaft with four openings per turn.

An opening 13 may be formed at the distal end of the needle shaft 11a of the present invention as shown in FIG. 4, and the opening 13 at the distal end may be closed as necessary.

The method of using the syringe equipped with the injection needle 10a of this embodiment is as follows.

Rotate the syringe with the needle and slowly puncture the heart wall. Once the distal end of the needle reaches the lower position of the heart muscle layer, the plunger is pushed to inject cell fluid into the necrosed myocardial tissue through a number of openings formed in the side of the shaft. Then, the needle is continuously rotated to penetrate into the endocardium, and then rotated in the reverse direction to pull the needle out. If necessary, the number of rotations and injections can be increased.

Compared to the first embodiment, the injection needle 11a of the second embodiment has the advantage of simultaneously injecting the cell fluid evenly at various positions of the myocardial tissue by only one injection.

[ Example  3]

Sustained blood flow is important for stem cells to differentiate into cardiomyocytes. The microchannels formed in the heart wall after the needle puncture are temporary and close slowly over time. In some cases, such microchannels may be rapidly closed, limiting sufficient blood flow to the injected stem cells.

In order to solve this problem, the shaft 11b of the needle 10b of the present invention may be made of a bioabsobale material. The bioabsorbable shaft forms a framework of microchannels in the heart wall to provide sufficient blood flow time for the stem cells to fully differentiate into cardiomyocytes and regenerate into myocardial tissue.

Bioabsorbable materials generally have a characteristic of being slowly hydrolyzed in the human body to form a single molecule and finally metabolized into H ₂ O and CO ₂ .

Such bioabsorbable materials include polylactic acid (poly lactide, "PLA"), polyglycolic acid (Poly glycolic acid, Polyglycolide, "PGA"), polylactic-glycolic acid (PLGA), polycaprolactone (Poly carprolactone (PCL) series, poly-dioxanon series, poly hydroxybutyrate series, aliphatic polyester and the like are already known. For example, polylactic acid (PLA) is a biodegradable suture material or a implantable implant material used in orthopedic surgery, which has been used in clinical practice for more than 30 years and has proven its safety. PLA is hydrolyzed in vivo to lactic acid, which is water soluble and finally metabolized to H ₂ O and CO ₂ .

Such bioabsorbable materials are mainly used in medical fields such as surgical sutures and stents for heart disease. The bioabsorbable material may be a material described above alone or a copolymer or blended material thereof.

The object of the present invention is that if it can be slowly biodegraded after punctured and inserted into human tissue, all of these properties are included in addition to the materials described above.

The bioabsorbable material is a plastic material. Very thin plastic tubes, such as needle shafts, can be manufactured with good compressive or tensile strength, but are generally weak to spin torque and easily twisted or broken. Thus, the portion of the shaft 11b connected to the hub 12b is preferably not vertical but within the same or slightly margin of error as the helical tilt angle (see FIGS. 5A and 5B). Since the shaft translates at the same time as the rotation, a spin torque does not occur in the shaft 11b of the hub 12b portion, and is pushed substantially in the helical direction.

On the other hand, the spirally wound bioabsorbable shaft 11b does not have rigidity as stainless steel. Therefore, it is difficult to puncture the heart wall in its original spiral shape, and if the barrel is rotated, it may be pushed outward.

The syringe according to the present embodiment may further include a guide body 40 to enable puncture of the tissue without deformation in the spiral needle during puncture of the tissue (see FIG. 6).

The guide body 40 is shaped like a pipe, and a spiral guide groove 41 is dug in its inner surface to accommodate the spiral shaft 11b. The depth and width of the guide grooves are preferably equal to or greater than the shaft diameter. The force exerted on the upper shaft during rotation is transmitted to the lower shaft without any deformation by the guide groove. Thus, the helical shaft 11b can be punctured into the heart wall without bending, while maintaining its original shape. A plurality of openings are formed on the side of the bioabsorbable shaft. Intracardiac blood flows along channels in the shaft and is supplied to the cell fluid through an opening in the shaft side. Over time, the bioabsorbable material slowly biodegrades, while stem cells are sufficiently stable in necrotic myocardial tissue, differentiate into cardiomyocytes, and develop into myocardial tissue. It is preferable that the protrusion 21 corresponding to the guide groove 41 is formed on the outer surface of the syringe barrel 20b.

The needle penetrates to the endocardium to form a channel, and then the shaft exposed to the epicardium is cut with a surgical cutter (scissors, cutters). The cut shaft ends are pushed further in with a thin iron core, and then the adhesive is applied as needed to complete the procedure.

[ Example  4]

FIG. 7A is an external view of a needle combined with two shaft members as an embodiment of the present invention, and FIGS. 7B and 7C are cross-sectional views of coupling members between members.

8 is a cross-sectional view of the syringe equipped with the needle of FIG. 7A as an embodiment of the present invention.

The needle shaft 11c of the present invention has a structure in which a bioabsorbable shaft (first shaft) 11c 'and a metallic shaft (second shaft) 11c' 'are coupled to each other, as shown in FIG. 7A. Can be. The bioabsorbable shaft 11c 'is inserted inside the heart wall as shown in FIG. The proximal portion of the metallic shaft 11c ″ is connected to the hub 12, and the distal portion is connected to the bioabsorbable shaft 11c ′.

As shown in FIG. 7B, the bioabsorbable shaft 11c ′ is preferably inserted into the metal shaft 11c ″.

FIG. 8 is a syringe equipped with the shaft 11c of FIG. 7A, which punctures the heart wall in the same manner as in the third embodiment. After puncturing to the predetermined portion of the metal shaft 11c '' and turning the needle in the reverse direction, the metal shaft 11c '' is easily pulled out, and only the bioabsorbable shaft 11c 'is located deep inside the heart wall. (See FIG. 9).

Meanwhile, as shown in FIG. 7C, the proximal end of the bioabsorbable shaft 11c ′ may be blocked. At this time, the bioabsorbable shaft (11c) is to form only the blood flow supply channel to the myocardial tissue without the role of cell fluid injection. Since the proximal end of the shaft 11c 'is blocked, there is no risk of blood bleeding into the epicardium. If necessary, the adhesive drug may be injected into the metal shaft 11c ″ to fill the needle hole.

[ Example  5]

The bioabsorbable shaft of Example 4 should be injected with cell fluid after the entire opening is inserted into the heart wall. If any of the openings are exposed to the outside, a significant amount of cell fluid can be lost through these exposed openings.

Therefore, it is inconvenient to use a new injection needle after a single procedure.

This embodiment provides a syringe that can be used multiple times without replacing the needle.

As shown in FIG. 10, the shaft 11d may be a combination of a considerably long bioabsorbable shaft 11d ′ and a metal shaft 11d ″ having a similar length. It is similar in shape to the shaft of FIG. 7A.

11 is a cross-sectional view of the syringe equipped with a needle. The bioabsorbable shaft 11d ′ having an opening at the side is positioned in the guide channel 42, and the metallic shaft 11d ″ without the opening is located in the guide groove 41. When the needle is rotated to reach the desired position of the bioabsorbable shaft and the cell fluid is injected, the opening of the bioabsorbable shaft 11d 'exposed to the outside is blocked by the guide channel 42 so that the cell fluid is not lost to the outside. Cell fluids are only injected through the openings penetrated into the heart tissue. The end of the shaft 11d 'is penetrated into the intraluminal cavity, and then the bioabsorbable shaft 11d' exposed to the epicardium is cut to complete the first procedure and continue to puncture the needle in the same manner to the other procedure site. .

The guide channel 42 may be formed by pushing a tube member 43 corresponding to the inside of the guide body 40 in which the guide groove is formed, as if there is a spiral passage in the wall of the pipe (see FIG. 11).

Experimental Example 1: Needle Injection Experiment

FIG. 12 (a) is a photograph of a straight-curve needle in which a middle portion of the shaft is bent by about 45 degrees, and is a needle mainly used for cell injection until now. Figure 12 (b) is a photograph of a needle having a spiral shaft according to the present invention.

Figure 13 (a) and (b) is a photograph of transplanting the cells in the heart of the rat heart is maintained using a conventional needle (Fig. 12 (a)), Figure 13 (a) is the first insertion of the needle It is a photograph and FIG. 13 (b) is a photograph five minutes after the procedure.

Figure 14 (a) and (b) is a picture of implanting the cells in the rat heart using the spiral needle of the present invention (Fig. 12 (b)), Figure 14 (a) is a picture when the needle first inserted, Figure 14 (b) is a photograph taken three minutes after the procedure.

In the case of conventional needles, a large amount of blood was ejected at the time of insertion of the needle due to difficulty in controlling the heart rhythm (see black arrow in FIG. 13 (a)). Because of this, it took about 5 minutes to insert the needle into two places to complete the injection of the cells (see black arrow in FIG. 13 (b)).

On the other hand, in the case of using the spiral needle of the present invention, despite the difficulty in controlling the heart rate of the rat, almost no ejection of blood was observed at the time of insertion of the needle (see black arrow in Fig. 14 (a)). It took about three minutes to complete the needle insertion in four places (see black arrow in FIG. 14 (b)).

As described above, the spiral needle of the present invention was confirmed that the cardiac blood was almost not ejected as compared with the conventional cell injection needle, and the procedure was performed quickly.

Experimental Example 2 Measurement of Cell Transplantation Expression

After transmitting the marker factor cy 5.5 to confirm the presence of the transplanted cells in the stem cells, the expression level of the stem cells transplanted into the heart was confirmed with xenogen equipment.

As shown in FIG. 15 (a), the expression state according to the cell number is used as an index, and the conventional straight-curve needle and the spiral of the present invention are applied to a myocardial infarction-induced rat model. After the implantation of 5 × 10 ⁶ cells by using a needle), the expression state is shown in FIG. 15 (b). Figure 15 (c) shows the color-bar of the xenogen equipment that can identify the cell number.

As shown in Figure 15 (b), the stem cell transplantation using the needle of the present invention (screw needle) is much larger than the conventional implantation using a straight-curve needle (straight-curve needle) Many cells were transplanted by color bars.

Experimental Example 3 Measurement of Changes in Cardiac Function

After the blood flow of the left anterior descending coronary artery of the rat model was surgically blocked to induce myocardial infarction, the change in heart function was measured by echocardiography. , (b) and (c) are shown graphically.

Figure 16 (a) is a result of injecting saline (saline) using a conventional straight curve needle, Figure 16 (b) is a human embryonic stem cell differentiated into endothelial cells using a conventional straight curve needle (hESC-EC) is the result of injection, Figure 16 (c) is a result of injecting human embryonic stem cells (hESC-EC) differentiated into endothelial cells using the spiral needle of the present invention.

Compared with the injection of physiological saline into the ischemic myocardium, the function of the heart transplanted with the stem cells (fractional shortening, FS) tended to be maintained, and the spiral injection of the present invention compared to the conventional straight curved needle. In the group using the needle (screw needle) showed a tendency to significantly improve the cardiac function.

1: syringe 10, 10a, 10b, 10c: needle
11, 11a, 11b, 11c, 11d: needle shaft
12, 12b: needle hub 13, 14: needle opening
20, 20b: syringe barrel 21: projection
30: plunger 40: guide sieve
41: guide groove 42: guide channel
43: tube member

Claims (10)

In the needle for injecting cells into the organ tissue of animals, including humans,
The shaft of the needle (needle shaft) is composed of a second shaft made of a metal spiral wound around the proximal portion, the first shaft of a spiral wound on the distal portion,
The first shaft is a polylactic acid (Poly lactic acid, Poly lactide, "PLA") series, poly glycolic acid (Poly glycolic acid, Polyglycolide, "PGA") series, polylactic-glycolic acid (PLGA), polycaprolactone ( Polycarprolactone (PCL) series, polydioxanone series, polyhydroxybutyrate series, aliphatic polyester, or a polymer selected from the group consisting of copolymers or blends thereof Made of bioabsorbale material,
When the needle is removed after the shaft is injected into the trachea tissue, the first injection shaft and the second shaft, the injection needle for cell injection, characterized in that coupled in a detachable form.
The needle of claim 1, wherein a plurality of openings are formed on side surfaces of the needle shaft.
delete delete delete delete The needle of claim 1, wherein the first shaft has a structure fitted to the second shaft.
A needle having a spiral shaft according to claim 1 or 2; A syringe barrel on which the needle is mounted; And a plunger inserted into the syringe barrel.
The syringe of claim 8, further comprising a guide body having a guide groove for receiving the helical shaft.
The syringe according to claim 9, wherein protrusions corresponding to inner grooves of the guide sieve are spirally formed on the outer surface of the syringe barrel.

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