JP5989039B2 - Syringe - Google Patents

Description

  The present invention relates to a syringe for injecting a substance to be injected into an injection target region of a living body without using an injection needle.

  In a needleless syringe that performs injection without going through an injection needle, a configuration may be employed in which an injection component is ejected by applying pressure to a storage chamber in which an injection solution is stored by a pressurized gas or a spring. However, it is difficult to say that needleless syringes having a conventionally known configuration are generally popular because the reproducibility of the injection volume and depth of the injection solution is not good.

  Then, the technique which adjusts the injection pressure of an injection solution in multiple steps using the explosive charge which consists of two types of powder mixtures of a high speed combustion powder and a low speed combustion powder is disclosed (for example, refer patent document 1). ). Specifically, the injection solution is first injected by applying a large force to the piston by burning the high-speed combustion powder. As a result, the injection solution penetrates the skin of the human body or the like and is sent into the body. Thereafter, a pressure that can diffuse into the skin is continuously applied by burning the low-speed combustion powder.

  Patent Document 2 discloses a technique of administering an injection solution in two stages in a needleless syringe, in which the injection solution is injected under high pressure, penetrated into the skin, and then applied to the injection solution. The pressure is lowered and the injection solution is dispersed in the skin. Furthermore, Patent Document 3 discloses a technique for adjusting the injection pressure of an injection solution with the strength of an electric current flowing using a magnet and a coil, in which high pressure is first applied to penetrate the skin, Next, the injection pressure is adjusted so as to obtain a substantially constant pressure in order to feed a desired injection solution.

  In addition, in a needleless syringe, the pressure applied to the injection solution is variously adjusted not only for the purpose of allowing the injection solution to reach the skin but also for other purposes. For example, Patent Document 4 shows that it is not preferable to increase the pressure applied to the injection solution after penetration through the skin in order to reduce noise generated when the injection solution is injected using a pressurized gas. .

  Here, an object to be injected by a needleless syringe is often a living body such as a human body. Then, consideration about the behavior of the injection liquid with respect to living body skin and the gel agent generally used for an experiment is shown (for example, refer nonpatent literature 1). Here, mention is made of the correlation between the depth of the hole formed by injection and the hole depth of the maximum diffusion width, the correlation between the Young's modulus of the skin and the hole depth, and the like. Further, Non-Patent Document 2 refers to the correlation between the diffusion width of the injection solution in the human skin and the nozzle diameter of the needleless syringe.

Special table 2003-534839 gazette U.S. Pat. No. 2,704,542 US Publication No. 2006/0258986 US Publication No. 2005/0010168

Joy Baxter, Samir Mitragotri, `` Jet-induced skin puncture and its impact on needle-free jet injections: Experimental studies and a predictive model '', Journal of Controlled Release (U.S.A.) 106 (2005), p361-373 Joy Schramm-Baxter, Samir Mitragotri, “Needle-free jet injections: dependence of jet penetration and dispersion in the skin on jet power”, Journal of Controlled Release (U.S.A.) 97 (2004), p527-535

  When an injection is performed on a living body, the components contained in the injection solution and the depth in the injection target region of the living body to which the component is to be fed differ depending on the purpose of injection. This is because the living body injection target area includes various structures such as skin, muscle, and internal organs, and the living tissue constituting these structures has its surface (when the injection is performed, the syringe is a structure) This is because the function varies depending on the depth from the surface touching the surface, and it is difficult to properly exert its effects unless the components in the injection solution reach the target biological tissue. .

  For example, human skin can be distinguished from the surface side into the epidermis, dermis, and subcutaneous tissue in layers, and the epidermis can be distinguished into the stratum corneum and intradermal. The stratum corneum is composed of keratinocytes, the skin is composed of dendritic cells and pigment cells, the dermis is composed of fibroblasts and collagen cells, and the subcutaneous tissue is composed of subcutaneous fat, etc. . And when injecting an injection solution for a predetermined purpose, it is preferable that the predetermined component contained therein is delivered accurately to the target tissue or the like.

  In order to efficiently inject without injecting the injection target substance into the injection target region of the living body, it is necessary to appropriately control the pressure applied to the injection target substance from the start to the end of the injection. That is, if the injection speed of the injection target substance by pressurization is too slow, the substance will bounce off the skin, whereas if it is too fast, the injection depth in the injection target area can be secured, but the Since the injection rate suitable for the diffusion of the substance is exceeded, it is considered that the substance is rebounded by an excessive supply and it is difficult to achieve the appropriate diffusion. In view of the above-described problems, the present invention provides a syringe that allows an injection target substance to be fed into an intended injection target region of a living body without using an injection needle and diffused widely in the depth thereof. Objective.

  In order to solve the above-mentioned problems, the present invention provides a syringe for injecting an injection target substance into an injection target region of a living body without using an injection needle. It was decided to adopt a configuration that adjusts in the pressure mode. By this different pressurization mode, it becomes possible to send the injection target substance into the living tissue at a desired depth in the injection target region.

  Specifically, the present invention is a syringe for injecting an injection target substance into an injection target region of a living body without going through an injection needle, and includes a sealing part for sealing the injection target substance, and a sealing part enclosed in the sealing part. A pressurizing section that pressurizes the injection target substance; and a flow path section that defines a flow path so that the injection target substance pressurized by the pressurization section is ejected to the injection target area. . The pressurizing unit increases the pressure to the injection target substance in the pressurization unit to the first peak pressure in order to penetrate the surface of the injection target region, and then sets the pressure to the injection target substance to the standby pressure. And pressurizing the injection target substance at the standby pressure, increasing the pressure to the injection target substance to a second peak pressure, and A second pressurizing mode for injecting the injection target substance.

In the syringe according to the present invention, the injection target substance to be injected into the injection target region of the living body is enclosed in the enclosing part, and pressure is applied to the injection object substance enclosed in the enclosing part, whereby the injection is performed. The movement of the target substance will be prompted. As a result, the injection target substance is injected into the target injection target region through the flow path portion. This injection target substance contains a component expected to have an effect inside the injection target region, and the pressure in the pressurizing part is the driving source at the time of injection as described above. Therefore, if injection by pressurization in the pressurization part is possible, the state of the injection target substance in the enclosing part, the specific state of the injection target substance such as liquid, gel-like fluid, powder, granular solid, etc. The physical form is not questioned.

  For example, the injection target substance is a liquid, and even if it is a solid, it may be a gel-like solid as long as fluidity enabling injection is ensured. The injection target substance includes a component to be sent to the injection target region of the living body, and the component may exist in a state dissolved in the injection target substance, or the component is simply mixed without being dissolved. It may be in the state where it was done. For example, as ingredients to be delivered, there are vaccines for antibody enhancement, proteins for cosmetics, cultured cells for hair regeneration, etc., so that these can be injected into fluids such as liquids and gels. By inclusion, a substance for injection is formed.

  Various pressurization sources can be used as the pressurization source for the injection target substance by the pressurization unit as long as the pressurization modes of the first pressurization mode and the second pressurization mode are possible. For example, those using elastic force by springs, those using pressurized gas, those using explosive combustion, those using electrical actuators (motors, piezo elements, etc.) for pressurization And as a pressure source.

  Here, the injection target substance can be appropriately injected into the injection target area of the living body by the two pressurization modes realized by the pressurization unit. In other words, by adopting the first pressurization mode and the second pressurization mode, the injection target substance is sent to the target injection depth of the injection target region such as the skin structure and diffused. Become. In the first pressurization mode, the pressurization pressure to the injection target substance is increased to the first peak pressure and then decreased to the standby pressure. Thereby, the surface of the injection target area | region of a biological body is first penetrated, and the injection target substance advances in the depth direction of the said area | region.

  Since the injection energy of the injection target substance is determined by the flow rate of the substance injected per unit time, the pressurization speed (pressure increase per unit time) of the injection target substance in the first pressurization mode is As it increases, the injection depth of the injection target substance in the first pressurization mode increases. In the first pressurization mode, the pressure increase is adjusted so that at least the injection target substance is given a pressure necessary to penetrate the surface of the injection target region.

  Here, the present applicant assumes the mechanism of injection into the injection target region by the injected injection target substance as follows. In addition, the applicant does not intend to adhere to this mechanism, and for the invention that exhibits the same effect as the present application as a result of pressure control on the injection target substance shown in the present application, a mechanism different from the mechanism is temporarily assumed. Even if it complies with the above, it is considered to belong to the category of the invention of the present application.

  When the injection target substance is injected into the injection target area, the tip of the flow of the pressurized injection target substance (jet flow) injected at the very beginning sharpens the injection target area, and the scraped scraps back flow. As a result of being lifted upward by the above, a hole is made, and the jet flow tip advances in the depth direction. As the tip of the jet stream becomes deeper, the jet stream's injection energy is lost by friction with the back flow, and when the injection energy is lost by the back flow and loses the ability to cut the injection target area, that is, the resistance of the back flow. The progress of the hole depth will be stopped when the energy is changed.

And if the jet flow is injected into the injection target area, the same amount of backflow will go up the hole in the opposite direction, so it is necessary to secure a hole diameter for the backflow to flow. Since tissue is inherently elastic, it tends to shrink and reduce the hole diameter. This contraction force narrows (reduces the diameter of) the backflow channel. Therefore, if the contraction force is relatively large with respect to the jet flow, the resistance due to the back flow increases, and the jet energy of the jet flow is balanced at a relatively shallow depth.

  Considering the invention according to the present application based on the above mechanism, injection formed to reach a certain injection depth when the pressure on the injection target substance rises to the first peak pressure and then falls to the standby pressure In a part of the penetration path of the target substance (tip part of the penetration path), the elastic force inherent to the injection target region of the living body becomes relatively large with respect to the jet flow, so that the diameter of the penetration path is contracted. It is thought that it is in a state. At this time, the pressure applied to the injection target substance at a position where the tip part of the injection target substance decompressed to the standby pressure does not reach the injection target region of the living body located at the tip part of the reduced diameter passage ( (Standby pressure) and the pressure due to the backflow from the injection target area of the living body are considered to be in a substantially balanced state. In this way, when a part of the through-passage is reduced in diameter, it is considered that the strength against the jet flow is higher than that of the part not reduced in diameter. And this improvement in strength means that it is difficult to secure a backflow path during repressurization in the second pressurization mode. Therefore, even if re-pressurization in the second pressurization mode is performed after reaching the standby pressure, the area through which the back flow passes is lost in the contracted through passage, so the jet flow does not reach the front end of the through passage, The pressure is mainly applied to the injection target substance in the through passage not reduced in diameter. For this reason, the penetration of the injection target substance is promoted in a direction in which the injection target substance spreads in the injection region of the living body more than the penetration path extends further in the depth direction, so that the injection target substance is diffused over a wide range. In other words, the first pressurization mode until reaching the standby pressure is a step capable of forming a state where diffusion should be performed, and the second pressurization mode is a step of accelerating the diffusion of the injection target substance in the formed state. It can also be said. In the second pressurization mode, the injection of the injection target substance at the target predetermined injection volume can be realized by increasing the pressurization to the injection target substance to the second peak pressure.

  The first peak pressure and standby pressure in the first pressurization mode described above and the second peak pressure in the second pressurization mode are appropriately determined according to the purpose of injection of the injection target substance. At this time, physical characteristics of the injection target area of the target living body, for example, Young's modulus of the skin, and the like may be considered. Moreover, the living body as an injection target of the syringe according to the present invention is not limited to humans, and may be livestock such as pigs and pets such as dogs.

  As described above, according to the syringe according to the present invention, it is possible to achieve the effect without unnecessarily increasing the injection depth by bringing the injection target substance to the standby pressure when the first pressure mode is reached to the second pressure mode. In particular, it is possible to diffuse the injection target substance within the injection target region. That is, the syringe according to the present invention can widely diffuse the injection target substance at a relatively shallow depth in the injection target region of the living body.

  In the syringe, the standby pressure may be a first predetermined ratio or less of the first peak pressure. The present applicant has found that if the ratio of the standby pressure to the first peak pressure is equal to or less than the first predetermined ratio, the above-described effective diffusion of the injection target substance can be realized. As a preferred example, the first predetermined ratio is set to 60%.

  In the syringe up to the above, the second peak pressure is not more than the first peak pressure, and a pressure difference between the first peak pressure and the second peak pressure is relative to the first peak pressure. The second predetermined ratio may be included. That is, the second peak pressure is set to be equal to or lower than the first peak pressure, but the pressure difference is suppressed so as not to exceed the second predetermined ratio with respect to the first pressure peak. Thereby, it becomes possible to realize injection of a target injection amount in the second pressurizing mode without unnecessarily increasing the injection depth.

  On the other hand, in the syringe up to the above, the second peak pressure may be a pressure exceeding the first peak pressure. Even if the second peak pressure exceeds the first peak pressure by the mechanism assumed as described above, once the injection target substance reaches the standby pressure, the effective injection target substance is diffused. It is promoted, and the mischievous increase in the injection depth can be suppressed. Depending on the physical characteristics of the injection target region of the living body, by increasing the second peak pressure in this way, injection of a target injection amount may be easily realized in the second pressurization mode.

  In the syringe described above, the rate of pressure increase from the standby pressure in the second pressurization mode to the arrival of the second peak pressure is the pressure from the start of pressurization in the first pressurization mode to the arrival of the first peak pressure. It may be set lower than the rate of increase. Thereby, it becomes possible to realize effective diffusion of the injection target substance by reaching the standby pressure in the first pressurization mode.

  Further, the injection amount of the injection target substance in the second pressurization mode may be set larger than the injection amount of the injection target substance in the first pressurization mode. In the first pressurizing mode until the standby pressure is reached, most of the injected injection target substance forms the injection target region in a state suitable for diffusion of the injection target substance in the injection target region as described above. The injection target substance is generally considered to be discharged outside the injection target area as a backflow. Thus, by relatively increasing the injection amount in the second pressurization mode in this way, a larger amount of the injection target substance can be diffused to the target depth of the injection target region and is included in the injection target substance. It is expected that the effects of the ingredients will be demonstrated.

  Here, in the syringe up to the above, the syringe further includes an ignition device including an ignition agent and a combustion product generated by the combustion of the ignition agent, and burns with the combustion product to generate a predetermined gas. A combustion chamber containing a gas generating agent, and the pressure in the combustion chamber may be configured to be pressurized against the injection target substance sealed in the sealing portion. In this case, the pressurizing unit sets a pressure increase generated by the combustion of the ignition agent in the ignition device as a pressurization transition to the first peak pressure in the first pressurization mode, and generates the gas. An increase in pressure due to the predetermined gas generated from the agent is defined as a pressure transition up to the second peak pressure in the second pressurization mode.

  That is, as a specific example for realizing the pressurization to the injection target substance in the first pressurization mode and the second pressurization mode, the pressure generated by the combustion of the explosive is applied to the drive source for injection of the injection target substance. It is possible to adopt a form that uses. In the syringe configured as described above, the pressure transition in the first pressurization mode is appropriately adjusted by appropriately adjusting the components of the ignition agent and the gas generating agent in the ignition device, the shape in the syringe, and the relative positional relationship. It is possible to suitably adjust the pressure transition in the second pressurizing mode. In addition, in the illustration of the drive source using such explosives, there is no intention to exclude the use of the drive source according to other modes. For example, one using an elastic force by a spring or the like, one using a pressurized gas, one using an electric actuator (motor, piezo element, etc.) for pressurization is adopted as the drive source. It doesn't matter.

  In the syringe, a pressure drop caused by the condensation of the combustion products in the first pressurizing mode in the combustion chamber may be a decrease in pressure from the first peak pressure to the standby pressure. By using the condensing action of the combustion products for the pressure effect, the kinetic energy of the injection target substance can be suppressed until the standby pressure is reached while maintaining the energy penetrating the surface of the injection target region of the living body, Injection at a shallower site in the injection target area of the living body becomes possible.

Further, in the syringe described above, the ignition completion time of the ignition agent is earlier than the combustion completion time of the gas generating agent, the combustion of the ignition agent is completed, and the pressure to the injection target substance is the first peak pressure. The gas generation rate from the gas generating agent may be increased in a stage where the gas generating agent is decreasing from the standby pressure to the standby pressure. That is, as long as the standby pressure in the first pressurization mode can be ensured, the combustion period of the igniting agent and the combustion period of the gas generating agent may partially overlap. In the case of overlapping, the pressure due to the combustion of the igniting agent and the pressure of the gas generated from the gas generating agent overlap and pressurize the target substance for injection. In addition, in order to adjust the combustion completion time of an ignition agent and a gas generating agent as mentioned above, each composition and composition ratio can be changed. Moreover, even if both have the same composition and composition ratio, you may change each shape and dimension. For example, when the state of the explosive is powder, the combustion completion time is faster than the combustion completion time of the explosive of the same composition formed in a lump. Furthermore, the combustion completion time can be adjusted by changing both the composition, shape, and dimensions. In this way, even when the igniting agent and the gas generating agent contain explosives of the same composition, the combustion completion time can be adjusted by adjusting the state, shape, dimensions, etc. of the explosive.

  Further, in the syringe up to the above, the igniting agent includes explosives containing zirconium and potassium perchlorate, explosives containing titanium hydride and potassium perchlorate, explosives containing titanium and potassium perchlorate, aluminum and perchlorate. Gunpowder containing potassium acid, gunpowder containing aluminum and bismuth oxide, gunpowder containing aluminum and molybdenum oxide, gunpowder containing aluminum and copper oxide, gunpowder containing aluminum and iron oxide, or a plurality of these An explosive consisting of a combination of As a feature of these igniting agents, even if the combustion product is generated in a high temperature state, even if gas is generated, it does not contain a gas component at normal temperature, so that when the combustion product comes into contact with the surface in the combustion chamber, it immediately condenses. Injection at a shallower site in the injection target area of the living body becomes possible.

  The injection target substance can be sent to the depth of the target injection target region of the living body without going through the injection needle and diffused widely at the depth.

It is a figure which shows schematic structure of the syringe which concerns on this invention. It is a figure which shows schematic structure of the initiator (ignition apparatus) with which the syringe shown in FIG. 1 is mounted | worn. It is a figure which shows the outline of a human skin structure. FIG. 2 is a diagram showing a change in pressure applied to an injection solution in the syringe shown in FIG. 1. It is a mode that this injection liquid diffuses in a human skin structure when the pressure of transition shown in Drawing 4 is applied to injection liquid. It is a 1st figure which shows the result of the injection experiment by the syringe which concerns on this invention. It is a 2nd figure which shows the result of the injection experiment by the syringe which concerns on this invention. It is a 3rd figure which shows the result of the injection experiment by the syringe which concerns on this invention.

  Hereinafter, a syringe 1 according to an embodiment of the present invention will be described with reference to the drawings. The configuration of the following embodiment is an exemplification, and the present invention is not limited to the configuration of this embodiment.

Here, FIG. 1 (a) is a cross-sectional view of the syringe 1, FIG. 1 (b) is a side view of the syringe 1 seen from the initiator 20, and FIG. 1 (c) shows the syringe 1 with the injection solution. It is the side view seen from the nozzle 4 side to inject. The syringe 1 has a syringe body 2, and a through-hole 14 extending in the axial direction and having a constant diameter along the axial direction is provided in the central portion of the syringe body 2. One end of the through hole 14 communicates with the combustion chamber 9 having a diameter larger than the diameter of the through hole 14, and the other end reaches the nozzle holder 5 side where the nozzle 4 is formed. Furthermore, an initiator 20 is installed on the opposite side of the combustion chamber 9 from the communication location with the through-hole 14 so that the ignition part faces the communication location.

  Here, an example of the initiator 20 will be described with reference to FIG. The initiator 20 is an electric ignition device, and a space for arranging the ignition agent 22 is defined in the cup 21 by a cup 21 whose surface is covered with an insulating cover. And the metal header 24 is arrange | positioned in the space, and the cylindrical charge holder 23 is provided in the upper surface. The charge holder 23 holds the ignition agent 22. A bridge wire 26 that electrically connects one conductive pin 28 and the metal header 24 is wired at the bottom of the ignition agent 22. The two conductive pins 28 are fixed to the metal header 24 via the insulator 25 so that they are insulated from each other when no voltage is applied. Furthermore, the opening of the cup 21 from which the two conductive pins 28 supported by the insulator 25 extend is protected by the resin 27 in a state in which the insulation between the conductive pins 28 is well maintained.

  In the initiator 20 configured as described above, when a voltage is applied between the two conductive pins 28 by the external power source, a current flows through the bridge wire 26, thereby burning the igniting agent 22. At this time, the combustion products resulting from the combustion of the igniting agent 22 are ejected from the opening of the charge holder 23. Therefore, in the present invention, the relative positional relationship of the initiator 20 with respect to the syringe body 2 is designed so that the combustion product of the igniting agent 22 in the initiator 20 flows into the combustion chamber 9. The initiator cap 12 is formed in a hook shape so as to be hooked on the outer surface of the initiator 20 and is fixed to the syringe body 2 with screws. Thereby, the initiator 20 is fixed to the syringe main body 2 by the initiator cap 12, and therefore, the initiator 20 itself can be prevented from dropping from the syringe main body 2 due to the pressure generated when the initiator 20 is ignited.

  The igniting agent 22 used in the syringe 1 is preferably an explosive containing zirconium and potassium perchlorate (ZPP), an explosive containing titanium hydride and potassium perchlorate (THPP), titanium and potassium perchlorate. Gunpowder containing (TiPP), Gunpowder containing aluminum and potassium perchlorate (APP), Gunpowder containing aluminum and bismuth oxide (ABO), Gunpowder containing aluminum and molybdenum oxide (AMO), Gunpowder containing aluminum and copper oxide (ACO) ), Explosives containing aluminum and iron oxide (AFO), or explosives composed of a combination of these explosives. These explosives generate high-temperature and high-pressure plasma at the time of combustion immediately after ignition, but exhibit a characteristic that the generated pressure rapidly decreases because the combustible organisms do not contain gas components when they become room temperature. This characteristic is a characteristic that favorably contributes to the formation of a pressurizing mode for the injection solution in the syringe 1 according to the present invention. This point will be described later. In addition, as long as the pressurization mode mentioned later is realizable, you may use explosives other than these as an ignition powder.

Here, in the combustion chamber 9, a columnar gas generating agent 30 is disposed that burns with a combustion product generated by the combustion of the igniting agent 22 and generates gas. As an example of the gas generating agent 30, a single base smokeless gunpowder composed of 98% by mass of nitrocellulose, 0.8% by mass of diphenylamine and 1.2% by mass of potassium sulfate can be mentioned. It is also possible to use various gas generating agents that are used in gas generators for airbags and gas generators for seat belt pretensioners. The gas generating agent 30 is different from the igniting agent 22 in that the predetermined gas generated during combustion contains a gas component even at room temperature, and therefore the rate of decrease in the generated pressure is extremely small compared to the igniting agent 22. Furthermore, although the combustion completion time at the time of combustion of the gas generating agent 30 is extremely longer than that of the igniting agent 22, the size, size, and shape of the gas generating agent 30 when disposed in the combustion chamber 9, particularly It is possible to change the combustion completion time of the gas generating agent 30 by adjusting the surface shape. This is because the state of contact of the igniting agent 22 flowing into the combustion chamber 9 with the combustion product depends on the surface shape of the gas generating agent 30 and the arrangement of the gas generating agent 30 in the combustion chamber 9. This is because it is considered to change depending on the relative positional relationship between the agent 30 and the ignition agent 22.

  Next, a metal piston 6 is disposed in the through hole 14 so as to be slidable in the through hole 14 along the axial direction, one end of which is exposed to the combustion chamber 9 side, and the other end is exposed to the other end. The sealing member 7 is integrally attached. Then, an injection solution ML that is an injection target substance injected by the syringe 1 is sealed in a space formed in the through hole 14 between the sealing member 7 and another sealing member 8. Therefore, the sealing member 7, 8 and the through hole 14 form a sealed portion of the syringe according to the present invention. The sealing members 7 and 8 prevent the injection liquid from leaking out when the injection liquid ML is sealed, and the injection liquid ML can smoothly move in the through hole 14 as the piston 6 slides. It is made of rubber with a thin coating of silicon oil on the surface.

  Here, the flow path portion of the syringe 1 according to the present invention is formed on the distal end side (the right side in FIG. 1) of the syringe 1. Specifically, a holder 5 in which a nozzle 4 for injecting the injection liquid ML is formed is provided on the distal end side of the syringe 1. The holder 5 is fixed to the end surface of the syringe body 2 with a gasket 3 interposed therebetween via a holder cap 13. The holder cap 13 is formed in a hook shape so as to be hooked to the holder 5, and is fixed to the syringe body 2 with screws. Thereby, the holder 5 is prevented from dropping from the syringe main body 2 due to the pressure applied to the injection liquid ML when the injection liquid ML is ejected.

  In addition, when the holder 5 is attached to the syringe body 2, a recess 10 that can accommodate the sealing member 8 is formed at a location facing the sealing member 8. The recess 10 has substantially the same diameter as the sealing member 8 and has a depth slightly longer than the length of the sealing member 8. Thereby, when pressure is applied to the piston 6 and the injection liquid ML moves to the distal end side of the syringe 1 together with the sealing members 7 and 8, the sealing member 8 can be accommodated in the recess 10. When the sealing member 8 is accommodated in the recess 10, the pressurized injection solution ML is released. Therefore, the flow path 11 is formed at a portion of the holder 5 that contacts the syringe body 2 so that the released injection liquid ML is guided to the nozzle 4. Thereby, the released injection liquid ML is ejected from the nozzle 4 to the injection target through the flow path 11. Moreover, it can avoid that injection | pouring of the injection liquid ML is inhibited by the sealing member 8 because the recessed part 10 has the depth which accommodates the sealing member 8. FIG.

  A plurality of nozzles 4 may be formed on the holder 5 or one nozzle 4 may be formed. When a plurality of nozzles are formed, a flow path corresponding to each nozzle is formed so that the injection solution released to each nozzle is fed. Further, when a plurality of nozzles 4 are formed, it is preferable that the nozzles are arranged at equal intervals around the central axis of the syringe 1 as shown in FIG. In the present embodiment, the three nozzles 4 in the holder 5 are arranged around the central axis of the syringe 1 at equal intervals. The diameter of the nozzle 4 is appropriately set in consideration of the injection target, the injection pressure applied to the injection liquid ML, the physical properties (viscosity) of the injection liquid, and the like.

  In the syringe 1 configured as described above, the combustion product or predetermined gas is generated in the combustion chamber 9 by the ignition agent 22 in the initiator 20 and the gas generating agent 30 disposed in the combustion chamber 9, and the piston 6. The pressure is applied to the injection liquid ML sealed in the through-hole 14 via. As a result, the injection liquid ML is pushed out to the distal end side of the syringe 1 with the sealing members 7 and 8, and when the sealing member 8 is accommodated in the recess 10, the injection liquid ML passes through the flow path 11 and the nozzle 4. , It will be injected into the injection object. Since pressure is applied to the injected injection liquid ML, it can penetrate the surface of the injection target object and reach the inside of the injection liquid, thereby achieving the purpose of injection in the syringe 1.

  Here, the injection target of the syringe 1 according to the present invention is a skin structure of a living body such as a human being or a domestic animal. In this specification, mainly referring to the action of the syringe 1 on human skin, FIG. 3 schematically shows the anatomical structure of human skin. The human skin is composed of the epidermis, dermis, subcutaneous tissue / muscle tissue in layers from the skin surface side to the depth direction, and the epidermis can be distinguished into the stratum corneum, intradermal and layered. Each layer of the skin structure is different also in the main cells constituting the tissue and the characteristics of the tissue.

  Specifically, the stratum corneum is mainly composed of keratinocytes and has a function as a barrier layer because it is located on the outermost surface side of the skin. In general, the thickness of the stratum corneum is about 0.01 to 0.015 mm, and the human surface is protected by keratinocytes. For this reason, a relatively high strength is also required to physically shield the external environment and the human body to some extent. The skin is composed of dendritic cells (Langerhans cells) and pigment cells (melanocytes), and the epidermis is formed by the stratum corneum and the skin, and the thickness of the epidermis is generally 0.1- It is about 2 mm. Dendritic cells in the skin are thought to be involved in antigen / antibody reactions. This is because the antigen-antibody reaction that activates the lymphocytes that recognize dendritic cells and play a role in foreign body attack is easily induced by taking up the antigen. On the other hand, pigment cells in the skin have a function of preventing the influence of ultraviolet rays irradiated from the external environment.

  Next, in the dermis, blood vessels and capillaries on the skin are intricately spread, and sweat glands for adjusting body temperature, hair roots of body hair (including head hair) and sebaceous glands associated therewith are also present in the dermis. To do. The dermis is a layer that connects the human body (subcutaneous tissue / muscle tissue) and the epidermis and includes fibroblasts and collagen cells. Therefore, the state of the dermis is largely involved in the generation of wrinkles and hair loss due to so-called lack of collagen or elastin.

  As described above, the human skin structure is generally formed in a layered manner, and inherent anatomical functions are exhibited by cells, tissues, and the like mainly contained in each layer. This means that when a medical treatment or the like is performed on the skin, it is desirable to inject a therapeutic component at the location (depth) of the skin structure according to the treatment purpose. . For example, since dendritic cells are present in the skin, a more effective antigen-antibody reaction can be expected by performing a vaccine injection here. However, with the conventional injection technique, it is difficult to inject a vaccine into the skin located at a relatively shallow site, and even if it is performed, it largely depends on the skill of a medical worker. Furthermore, since pigment cells exist in the skin, it is required to inject specific components for whitening into the skin even when performing cosmetic treatment for so-called whitening. It is difficult to pass.

  Next, since fibroblasts and collagen cells exist in the dermis, proteins, enzymes, vitamins, amino acids, minerals, sugars, nucleic acids, various growth factors (epithelial cells and fibroblasts) are used to remove skin wrinkles. When cells are injected into the dermis, an effective cosmetic treatment effect is expected. However, since the dermis is located at a relatively shallow site as in the skin, there are many difficulties in cosmetic treatment by injection in the prior art. Also, in hair regeneration treatment, since the hair root is located in the dermis, for hair regeneration treatment, stem cell injection method or stem cell in which hair dermal papilla cells, epidermal stem cells, etc. are self-cultured and autotransplanted into the scalp. It is said that it is preferable to inject several kinds of growth factors and nutrients extracted from the dermis near the dermis.

In this way, the substance to be injected according to the purpose of treatment for the skin and the position (depth) in the skin structure where it is desired to be injected individually correspond, but in the prior art, the injection position is adjusted. Difficult to do. In the syringe 1 according to the present invention, it is possible to suitably adjust the depth at which the injection solution reaches the skin structure by adjusting the pressure applied to the injection solution. As described above, substances to be injected into the skin structure (injection target substance) vary depending on the treatment purpose, and therefore, in the following description, the injection target substance is generically referred to as “injection solution”. However, this is not intended to limit the content or form of the injected substance. In the injection target substance, the component to be delivered to the skin structure may or may not be dissolved, and the injection target substance can be injected from the nozzle 4 to the skin structure by pressurization. If it exists, the specific form is not ask | required and various forms, such as a liquid and a gel form, are employable.

  For example, the target substance for injection in the cosmetic treatment includes proteins, enzymes, vitamins, amino acids, minerals, saccharides, nucleic acids, various growth factors (epithelial cells, fibroblasts, etc.) for whitening and wrinkle removal. Examples of the substance to be injected in hair regeneration treatment include dermal papilla cells, hair root stem cells, epidermal stem cells, HARG cocktail, and hair for transplantation.

  Next, the specific pressurization form to the injection solution performed in the syringe 1 is demonstrated based on FIG. FIG. 4 shows a change in pressure applied to the injection solution sealed in the through hole 14 via the piston 6 by appropriately adjusting the combination of the ignition agent 22 and the gas generating agent 30 included in the syringe 1. . The horizontal axis in FIG. 4 represents elapsed time in milliseconds, and the vertical axis represents applied pressure in MPa. This pressure can be measured by installing a pressure gauge in a pressure measurement port (not shown in FIG. 1) provided to connect to the combustion chamber 9 in the syringe body 2. In the example shown in FIG. 4, the pressure transition when the three types of amounts of the gas generating agent 30 are combined with the same amount of ZPP (including zirconium and potassium perchlorate) as the igniting agent 22 is L1, L2. , L3 as shown in FIG.

  Here, the pressure transitions L1 to L3 in the syringe 1 according to the present invention will be described. These pressure transitions have a common technical feature. First, this will be described based on the pressure transition L2. In the pressure transition in the present invention, combustion of the igniting agent 22 is started immediately after energization of the initiator 20, so that the pressure suddenly reaches the first pressure peak value P1max from the zero state, and then the standby pressure Pw2 (The standby pressure is represented by Pw1 in the pressure transition L1 and the standby pressure Pw3 in the pressure transition L3). The process of applying pressure to the injection by the pressure transition so far is referred to as a first pressurizing mode. After that, the pressure rises again and reaches the second peak pressure P2max2 (the second peak pressure is represented by P2max1 in the pressure transition L1 and the second peak pressure is represented by P2max3 in the pressure transition L3), and then gradually decreases. Go. The step of applying pressure to the injection solution by the pressure transition rising from the standby pressure to the second peak pressure is referred to as a second pressurizing mode. In this way, each of the pressure transitions L1 to L3 is configured by the first pressurization mode and the second pressurization mode.

  Thus, two different pressurization modes in one pressure transition are realized by the igniting agent 22 and the gas generating agent 30 having different combustion forms. That is, the combustion form of the igniting agent 22 is characterized by instantaneous combustion by energization of the initiator 20, and when the combustion gas generated as typified by ZPP is condensed at room temperature, no gas component is contained therein. As a result, the pressure applied to the injection solution drops rapidly. Therefore, the pressure transition in the first pressurization mode is completed in the minute time Δt shown in FIG. On the other hand, high-temperature combustion products generated by the combustion of the igniting agent 22 flow into the combustion chamber 9 and burn the gas generating agent 30 disposed there, whereby the gas generating agent 30 starts to burn. Therefore, during the pressure transition in the first pressurization mode or immediately after the end of the first pressurization mode, the gas generating agent 30 burns and a predetermined gas is generated therefrom. The generation rate of the gas from the gas generating agent 30 is much slower than the generation rate of the combustion product from the igniting agent 22. In other words, the combustion completion time of the gas generating agent 30 is the combustion rate of the igniting agent 22. Longer than completion time. Therefore, as is apparent from FIG. 4, the pressure increase rate until the second peak pressure P2max2 reaches the second peak pressure P2max2 from the standby pressure Pw2 is drawn more slowly than the pressure increase rate at the time of ignition of the igniting agent 22. . This also applies to the pressure transitions L1 and L3.

The conceptual injection state of the injection solution in the human skin structure will now be described with reference to FIG. In the first pressurizing mode performed during the minute time Δt (the time from energization at the initiator 20 until reaching the standby pressure Pw2), a minute amount of injection solution is ejected from the syringe 1 as shown in FIG. . In the injection of a minute amount of injection solution, the injection amount per unit time, that is, the energy amount of the injection solution injected in accordance with the injection flow rate is determined by the following equation 1.
P = 1/8 · πρD ² u ³ (Expression 1)
P: energy of injection solution ρ: density of injection solution, D: diameter of nozzle 4, u: injection speed of injection solution

  In addition, this Formula 1 only calculates the energy amount which the injected injection solution has, and the said formula alone is not enough to explain the adjustment of the injection depth in the skin structure. That is, it is necessary to perform pressure control according to the present invention to adjust the injection depth. Therefore, the pressure control according to the present invention will be described below with respect to the adjustment of the injection depth in the skin structure while considering Equation 1.

  In the first pressurizing mode, since the pressure transition from the zero pressure state to the standby pressure through the peak pressure P1max is performed in a very short time, the process of injecting the injection solution having high energy to the skin is also performed. I can say that. As a result, the injection solution injected in the first pressurization mode penetrates the outermost surface of the skin and erodes into the skin (in FIG. 5A, the injection injection solution is represented by S1). . In addition, it is thought that the injection depth at this time becomes deep, so that the energy of the injection injection liquid at the time of the 1st pressurization mode represented by Formula 1 becomes large. Here, looking at Equation 1, the energy P of the injected injection solution is proportional to the product of the cube of the injection speed u of the injection solution and the density of the injection solution, so that the energy of the injected injection solution increases as the peak pressure P1max increases. P increases, and the energy P decreases as the minute time Δt during which the first pressurization mode is executed decreases. Therefore, by adjusting this energy P, it becomes possible to adjust the injection depth that the injection solution can reach within the skin. FIG. 5 (a) schematically shows a situation in which the injection solution reaches the layer portion of the epidermis in the human skin structure, but the injection in the first pressurizing mode is performed by adjusting the amount of energy. The depth can be made deeper or shallower.

Here, with respect to the standby pressure reached in the first pressurization mode, the erosion in the injection depth direction inside the skin structure of the injected injection solution in the first pressurization mode is mitigated, and the skin structure The pressure is such that the diameter of the through passage in a part of the formed through passage of the injection solution can be contracted. Here, after increasing to the peak pressure P1max and lowering to the standby pressure, the amount of energy of the injection solution decreases, so that the erosion to the skin by the injection solution is alleviated, and the injected injection solution is the deepest part of the skin structure. It will not reach the department. Furthermore, since the skin structure of a living body has a certain elastic force, the diameter of the through-passage is formed on a part of the through-passage already formed by the elastic force, particularly on the distal end side (the back side in the depth direction). Can be contracted by the elastic force with little or no injection. As a result, when the standby pressure is reached in the first pressurizing mode, a reduced diameter state is formed on the distal end side of the through passage, and a non-reduced state is maintained on the proximal end side of the through passage. A difference in strength with respect to the pressure of the injection solution is produced between the distal end side and the proximal end side of the through passage. That is, the strength of the distal end side of the through passage is relatively higher than the proximal end side. As a result, during re-pressurization in the second pressurization mode, which will be described later, the pressure of the injection solution is uniformly applied to the entire penetrating path during re-pressurization in the second pressurization mode, but the penetration in the non-diameter state Since the path portion is relatively enlarged, the strength is weaker than that of the reduced diameter portion, which is considered to contribute to the diffusion of the injection solution. From the above, the standby pressure is such that the distal end side of the through-passage is contracted by the elastic force from the skin structure in the second pressurization mode described later, that is, the through-passage that can ensure injection solution diffusion in the second pressurization mode. It is desirable that the pressure is lowered from the peak pressure P1max in the first pressurizing mode to such an extent that a difference in intensity is generated. For example, the standby pressure is preferably 50% or less of the peak pressure P1max.

  Next, in the second pressurization mode, a pressure transition that rises from the standby pressure Pw2 to the second peak pressure P2max2 is drawn. From the state where it is estimated that the difference in strength is generated in the through passage formed by the injection solution by the pressure of the injection solution reaching the standby pressure Pw2 in the first pressurization mode, the second pressurization mode When the pressure of the injection solution is increased again, it is considered that the injection solution confined in the through-passage whose diameter is contracted is pressurized again. However, the injection solution injected in the second pressurization mode pressurizes the skin structure through the injection solution in the non-diametered part rather than directly acting on the bottom of the through-passage due to the above difference in strength. More than the further erosion in the depth direction, the penetration into the inside of the skin structure is generated from the through passage in the non-diameter state. In other words, it is considered that the injection solution diffuses into the tissue of the skin structure through the portion of the through-passage in a non-diameter state that is considered to have a relatively low strength against pressure (in FIG. 5B). The injection solution diffusing in the second pressurization mode is represented by S2.) Further, since the rate of pressure increase during the second pressurization mode is more gradual than the rate of pressure increase during the first pressurization mode, the layered structure of the skin structure can be obtained without unnecessarily increasing the injection depth of the injection solution. The injection solution can be diffused into the skin along the extending direction of the tissue. FIG. 5 (b) is merely a conceptual representation of the above-described diffusion state, and when the injection depth is set to a different depth in FIG. 5 (a), the diffusion state is also different. It is also possible to diffuse so that it penetrates to a part closer to the skin or the dermis.

  The time during which the second pressurization mode is continued is determined according to the amount of injection solution (injection amount) ejected by the syringe 1. After the second pressure peak P2max2 elapses, the pressure applied to the injection solution gradually decreases, but when the injection solution ejected from the nozzle 4 runs out, the pressure becomes zero, and the second pressurization mode is finish. In addition, since the second pressurization mode is intended to diffuse the injection solution to a desired depth of the skin structure, the amount of the injection solution ejected from the syringe 1 in the second pressurization mode is the first pressurization mode. It is preferable that the amount of the injection solution injected in is larger. This is sufficiently realizable because the first pressurizing mode is performed within the minute time Δt as described above.

  Thus, in the syringe 1 which concerns on this invention, it passes through the standby pressure in a 1st pressurization mode, and passes through the pressure transition of the spreading | diffusion of the injection liquid by a 2nd pressurization mode, By the desired depth in a skin structure An injection solution can be fed. In particular, the pressurization in the second pressurization mode is mainly used for the diffusion of the injection solution, and it is avoided that the injection depth is excessively deepened. It becomes possible to diffuse accurately.

  Here, each of pressure transition L1, L2, L3 shown in FIG. 4 is demonstrated. In these pressure transitions, by using the same initiator 20, the peak pressure in the first pressurizing mode is approximately equal to P1max. Although the standby pressure varies in the range of Pw1 to Pw3, as described above, if the standby pressure drops to some extent from the peak pressure in the first pressurization mode, the skin structure of the injected injection solution in the first pressurization mode The erosion in the injection depth direction inside the body is mitigated, and a pressure capable of contracting the diameter of the penetrating path in a part of the penetrating path of the injection solution provided in the skin structure can be obtained. Even when the same initiator 20 is used as described above, the amount of the gas generating agent 30 disposed in the combustion chamber 9 is different, so that the pressure transition in the second pressurizing mode is changed. It changes as shown in FIG. Specifically, in the case of the pressure transition L1, the amount of the gas generating agent 30 is the maximum, in the case of the pressure transition L3, the amount of the gas generating agent 30 is the minimum, and in the case of the pressure transition L2, the amount of the gas generating agent 30 is Intermediate amount. Therefore, the peak pressure in the second pressurizing mode has a relationship of P2max1 of the pressure transition L1> P2max2 of the pressure transition L2> P2max3 of the pressure transition L3. According to such three kinds of pressure transitions, the speed at which the injection solution is diffused and the amount of the injection solution to be diffused can be varied at substantially the same injection depth.

  The peak pressure P2max3 in the pressure transition L3 is a value lower than the peak pressure P1max in the first pressurization mode. At this time, the pressure difference between P1max and P2max3 is kept within a predetermined ratio with respect to P1max. This is different from the pressure transition according to the prior art in order to send the injection solution to a desired depth in the skin structure, and the diffusion of the injection solution in the second pressurization mode through the standby pressure in the first pressurization mode. This is to clarify the pressure transition. An example of the predetermined ratio is 60% of P1max.

  Moreover, the peak pressures P2max1 and P2max2 in the second pressurization mode in the pressure transitions L1 and L2 are values that exceed the peak pressure P1max in the first pressurization mode. These peak pressures P2max1 and P2max2 are appropriately set in order to achieve the target injection amount.

  The embodiments described above are based on the assumption of a human skin structure, but the syringe according to the present invention can be used as a syringe for animals (domestic animals, pets, etc.) in addition to humans. In this case, the type and amount of the ignition agent 22 mounted on the initiator 20 and the type and amount of the gas generating agent 30 are appropriately adjusted in consideration of the characteristics of the skin structure of the injection target, such as Young's modulus.

  In the above-described embodiment, the injection target substance is applied with pressure in the syringe 1. However, the injection target substance is a powder, a granular solid, or the like as long as it can be injected from the syringe 1. It doesn't matter.

Here, about the injection experiment (experiments 1-4) performed using the syringe 1 which concerns on this invention, the experimental condition and experimental result are shown below. In addition, the following experimental conditions are set for the purpose of intensively diffusing the injection solution into the skin layer of the pig, which is the injection target.
<Experimental conditions>
(About syringe 1)
87 mg of ZPP (zirconium / potassium perchlorate) mixture was used for the igniting agent 22 of the initiator 20, and a single base propellant was used for the gas generating agent 30 in the amount shown in Table 1 below. In addition, the diameter of the nozzle 4 is 0.1 mm, and the three nozzles 4 are arranged concentrically.
Moreover, the component ratio of a single base propellant is as follows.
Nitrocellulose: 98.1% by weight
Diphenylamine: 0.8% by weight
Potassium sulfate: 1.1% by weight
Graphite (outside split): Trace amount (for injection target)
In this example, the skin part of the abdomen of the pig was used as the injection target. Specifically, after slaughtering pigs, the skin part was peeled off, and those stored for 6 days in physiological saline at 4 ° C. (refrigerated storage) and those thawed after freezing at −70 ° C. were prepared. .
(About injection solution)
A colored aqueous solution (methylene blue) was used in order to make it easier to grasp the diffusion state of the injection solution after injection.

<Experimental result>
Next, experimental results according to the above experimental conditions are shown below. FIG. 6A is a diagram of a surface of pig skin and a cross-sectional view (AA cross-section) thereof as a result of injection in Experiment 3. FIG. 6B is a diagram of the surface of the pig's skin as a result of injection in Experiment 4 and a cross-sectional view thereof (BB cross-section). Furthermore, FIG. 6C is a graph showing the change in pressure applied to the injection solution in each of Experiments 1 to 4. Table 2 below summarizes the predetermined pressure values in the pressure transition and the arrival time to the pressure. The pressure applied to the injection solution was measured with an electrostrictive element (piezo element) at a detection frequency of 100,000 times per second, that is, every 0.01 milliseconds. Moreover, the maximum pressure detected immediately after the initiator 20 act | operated was employ | adopted for the 1st peak pressure shown in following Table 2. FIG. The standby pressure is 0.05 ms before and after the lowest pressure recorded during the period in which the pressure drops from the first peak pressure until the gas generating agent 30 is completely ignited after the initiator 20 is activated. The average value of data including (that is, data of 5 points before and after) was adopted. And the maximum pressure that appeared after reaching the standby pressure was adopted as the second peak pressure. Each arrival time in Table 2 means the time until each pressure is reached starting from the time when the ignition current is passed through the initiator 20.

When the above experimental results are analyzed, in Experiments 1, 2, and 3, the injection solution injected from all three nozzles 4 provided in the syringe 1 is diffused at the desired injection depth in the skin layer of the pig. I was able to. For example, as shown in FIG. 6A corresponding to Experiment 3, it can be seen from the bird's-eye view from the skin surface that the injection marks spread at the same size in three places. Moreover, in the cross section, the injection solution does not spread unnecessarily to the fat layer or the muscle layer, but diffuses while remaining in the skin layer. If this injection solution is a vaccine, it can be intensively sent and diffused in a region where an effective antigen-antibody reaction can be expected. In Experiments 1 and 2 (not shown), as in Experiment 3 shown in FIG. 6A, effective diffusion of the injection solution was confirmed.

  On the other hand, in Experiment 4, about the injection liquid inject | emitted from one nozzle among the three nozzles 4, unlike Experiments 1-3, the injection liquid has spread a little in the fat layer or the muscle layer ( (See the cross-sectional view shown in FIG. 6B corresponding to Experiment 4.) 6B shows that the size of the injection mark corresponding to the cross-sectional view is smaller than the other two injection marks. This is because, in a small injection mark, as shown in the cross-sectional view, the injection solution reaches a deeper position of the injection target, and the amount of the injection solution that can be confirmed from the surface is reduced. However, in the two nozzles other than the nozzle shown in FIG. 6B, although not shown, effective diffusion of the injection solution was confirmed as in Experiments 1 to 3.

  Based on the above, if the standby pressure ratio (defined as a value obtained by dividing the standby pressure by the first peak pressure) is lower than a predetermined value, at least the injection solution injected from any one of the nozzles 4 is used. It can be effectively diffused into the skin layer of pigs, and the significance of practical use can be found. More preferably, if the standby pressure ratio is 0.50 or less, it is considered that effective diffusion of the injection solution injected from all three nozzles 4 is realized as shown in Experiments 1 to 3. . In the conventional needleless syringe, the syringe according to the present invention is considered in consideration of the fact that the injection solution has been fed deep inside the injection target so that the injection mark cannot be confirmed even when viewed from the skin surface as in the present invention. It can be said that 1 has a useful effect that could never be realized with a conventional needleless syringe.

<Other examples>
According to the syringe 1 according to the present invention, in addition to the case where the above-mentioned injection solution is injected into the skin structure, for example, in the field of regenerative medicine, cells to be injected or scaffold cells / scaffolds with cultured cells and stem cells Etc. can be seeded. For example, as disclosed in JP-A-2008-206477, cells that can be appropriately determined by those skilled in the art depending on the site to be transplanted and the purpose of recellularization, such as endothelial cells, endothelial precursor cells, bone marrow cells, and prebones Blast cells, chondrocytes, fibroblasts, skin cells, muscle cells, liver cells, kidney cells, intestinal cells, stem cells, and any other cells considered in the field of regenerative medicine can be injected with the syringe 1. . More specifically, the liquid (cell suspension) containing the cells to be seeded is accommodated in the through-hole 14 by the sealing members 7 and 8, and the first pressurization mode and the second addition described above are accommodated. By applying pressure through the pressure transition in the pressure mode, predetermined cells are injected and transplanted at the site to be transplanted.

  Furthermore, the syringe 1 according to the present invention can also be used for delivery of DNA or the like to cells, scaffold tissue, scaffolds, etc. as described in JP-T-2007-525192. In this case, it can be said that the use of the syringe 1 according to the present invention is more preferable than the case of delivery using a needle because the influence on the cells, the scaffold tissue, the scaffold and the like can be suppressed.

  Furthermore, the syringe 1 according to the present invention is suitable also when various genes, tumor suppressor cells, lipid envelopes, etc. are directly delivered to a target tissue or when an antigen gene is administered to enhance immunity against a pathogen. Used for. In addition, in the field of various disease treatments (fields described in JP2008-508881, JP2010-503616, etc.), immunomedicine (fields described in JP2005-523679, etc.), etc. The syringe 1 can be used, and the field in which the syringe 1 can be used is not intentionally limited.

DESCRIPTION OF SYMBOLS 1 ... Syringe 2 ... Syringe body 4 ... Nozzle 5 ... Holder 6 ... Piston 7, 8 ... Sealing member 9 ... Combustion chamber 10. ...... Recess 11 ... Flow path 20 ... Initiator 22 ... Ignition agent 30 ... Gas generating agent

Claims (9)

A syringe for injecting an injection target substance into an injection target region of a living body without going through an injection needle,
An enclosing portion for enclosing the injectable substance;
A pressurizing unit that pressurizes the injection target substance enclosed in the encapsulating unit;
A flow path section that defines a flow path so that the injection target substance pressurized by the pressurization section is ejected to the injection target area, and
The pressurizing part is
In order to penetrate the surface of the injection target region, the pressure applied to the injection target substance in the pressurizing unit is increased to the first peak pressure, and then the pressure applied to the injection target substance is decreased to the standby pressure. Pressure mode,
Pressurizing the injection target substance at the standby pressure, raising the pressure to the injection target substance to a second peak pressure, and injecting the injection target substance at a predetermined injection amount. There are two pressure modes , the pressure mode ,
The syringe in which the ratio of the standby pressure to the first peak pressure in the first pressurization mode is 50% or less.   The syringe according to claim 1, wherein a ratio of the standby pressure to the first peak pressure is 40% to 50%. The pressurizing part is
Ignition device including an igniting agent that generates high-temperature and high-pressure plasma at the time of combustion immediately after ignition and then exhibits a pressure characteristic that the generated pressure is reduced when the combustion product condenses and the combustion product does not contain a gas component When,
Combustion product generated by the combustion of the igniting agent is contained in a combustion chamber into which the combustion product flows, and is composed of a gas generating agent that burns with the combustion product and generates a predetermined gas,
The syringe according to claim 1 or 2, wherein the standby pressure is a pressure when the combustion product is condensed and the gaseous substance is no longer contained due to the combustion product condensing.   The syringe according to any one of claims 1 to 3, wherein in the standby pressure, erosion in the injection depth direction inside the injection target region is alleviated. The pressure increase rate from the standby pressure in the second pressurization mode to the arrival of the second peak pressure is lower than the pressure increase rate from the start of pressurization in the first pressurization mode to the arrival of the first peak pressure.
The syringe according to any one of claims 1 to 4.   The injection amount of the injection target substance in the second pressurization mode is larger than the injection amount of the injection target substance in the first pressurization mode. Syringe. The pressurizing part is
After increasing the pressure applied to the injection target substance to the first peak pressure in order to penetrate the surface of the injection target region by the pressure increase generated by the combustion of the ignition agent in the ignition device, the ignition agent The first pressurizing mode for lowering the pressure to the injection target substance to the standby pressure by the pressure characteristic of
Pressurizing the injection target substance at the standby pressure by the pressure increase due to the predetermined gas generated from the gas generating agent, increasing the pressure to the injection target substance to the second peak pressure, The second pressurization mode for injecting the injection target substance in a predetermined injection amount;
The syringe according to claim 3, wherein The ignition completion time of the ignition agent is earlier than the combustion completion time of the gas generating agent,
In the stage where combustion of the igniting agent is finished and the pressure to the injection target substance is decreasing from the first peak pressure to the standby pressure, the gas generation rate from the gas generating agent is increased. The syringe according to claim 7.   The igniting agent includes explosives including zirconium and potassium perchlorate, explosives including titanium hydride and potassium perchlorate, explosives including titanium and potassium perchlorate, explosives including aluminum and potassium perchlorate, aluminum and oxidation. A gunpowder containing bismuth, a gunpowder containing aluminum and molybdenum oxide, a gunpowder containing aluminum and copper oxide, a gunpowder containing aluminum and iron oxide, or a gunpowder comprising a combination of these. Item 9. The syringe according to item 7 or item 8.