JP7776843B1 - Fluid Delivery Device - Google Patents

Abstract

A fluid delivery device that can be easily reused is provided.
[Solution] The present disclosure relates to a fluid delivery device that delivers fluid by contacting a microneedle with biological tissue, comprising a base portion having an electrode portion connected to a power supply means, and a cap portion that is arranged to cover the electrode portion and is detachable from the base portion, the cap portion incorporating a fluid holding portion that supplies fluid to the microneedle, and is arranged so that the fluid holding portion comes into contact with the electrode portion when the cap portion is attached to the base portion.
[Selected Figure] Figure 1

Description

The present disclosure relates to a fluid delivery device.

Iontophoresis is a conventional medication method that promotes drug penetration by passing a small electric current through the body. Because iontophoresis allows drugs to be administered directly into blood vessels or the affected area, it has the advantage of being able to administer drugs more efficiently and minimizing side effects compared to conventional oral medication.

The present inventors have developed a porous microneedle with a fixed negative charge through chemical modification to generate a large electroosmotic flow on the positive electrode side (see, for example, Patent Document 1). It has been reported that this microneedle can deliver drugs under the skin regardless of the drug's charge, i.e., regardless of the direction of electrophoresis.

In response to this, the present inventors have developed an electroosmotic flow pump that uses a material with a fixed negative charge on the positive electrode side and a material with a fixed positive charge on the negative electrode side, enabling the supply of drugs to the surface of the skin or tissue using electroosmotic flow from both the positive and negative electrode sides without interfering with drug penetration on the negative electrode side (see, for example, Patent Document 2).

JP 2022-83780 A JP 2023-69170 A

The microneedles described in Patent Document 1 allow drugs to penetrate beneath the skin regardless of the charge of the drug, i.e., regardless of the direction of electrophoresis. Furthermore, the electroosmotic pump described in Patent Document 2 can supply drugs to the surface of the skin or tissue from both the positive and negative poles, thereby increasing the amount of drug administered. However, existing technologies leave room for improvement in terms of easily and repeatedly supplying drugs to biological tissue.

The present disclosure has been made in consideration of the above problems, and its purpose is to provide a fluid delivery device that can be easily used repeatedly.

According to the present disclosure, there is provided a fluid delivery device that delivers a fluid by bringing a microneedle into contact with biological tissue, comprising:
a base portion having an electrode portion connected to a power supply means;
a cap portion disposed to cover the electrode portion and detachable from the base portion,
The cap portion has a built-in fluid holding portion for supplying a fluid to the microneedle,
There is provided a fluid delivery device in which the fluid holding portion is arranged to contact the electrode portion when the cap portion is attached to the base portion.

The present disclosure provides a fluid delivery device that can be easily reused.

1 is a cross-sectional view illustrating a configuration example of a fluid delivery device according to an embodiment of the present disclosure. 2 is a partial enlarged view of the fluid delivery device of FIG. 1. 2A-2C are cross-sectional views of the fluid delivery device of FIG. 1 at different angles. 2 is a perspective view of a cap portion of the fluid delivery device of FIG. 1. FIG. FIG. 2 is a conceptual diagram for explaining the fluid delivery device according to the embodiment. FIG. 10A is a perspective view showing an array of positive and negative microneedles of the fluid delivery device according to the embodiment, and FIG. 10B is an enlarged side view of one negative microneedle. FIG. 10 is a conceptual diagram for explaining a modified example of the fluid delivery device of the present embodiment. 8 is a cross-sectional view of the fluid delivery device of FIG. 7 in use.

Preferred embodiments of the present disclosure will be described in detail below with reference to the accompanying drawings. Note that in this specification and drawings, components having substantially the same functional configuration will be assigned the same reference numerals, and redundant explanations will be omitted.

The fluid delivery device 100 shown in Figure 1 is a fluid delivery device that delivers fluid by bringing microneedles 130 into contact with biological tissue (i.e., injecting fluid into biological tissue).

The fluid delivery device 100 comprises a base portion 110 and a cap portion 120.

As shown in FIG. 2, the base portion 110 has an electrode portion 111 connected to a power supply means. The electrode portion 111 has, for example, a first electrode 111a and a second electrode 111b. Each electrode may be formed by a screw or other conductive material. In this example, the screw forming the electrode is inserted from inside the base portion, and the tip of the screw (through the partition) protrudes toward the outside of the base portion (inside the cap portion 120). Either the first electrode 111a or the second electrode 111b may be positive and the other negative. The power supply means is preferably, for example, a dry cell battery 113, but is not limited to this and may be any power source such as an AC power source. FIG. 1 shows the base portion 110 with the battery cover removed so that the dry cell battery can be replaced, and FIG. 3 shows the base portion 110 with the battery cover 115 attached.

The cap portion 120 is disposed so as to cover the electrode portion 111, and is detachable from the base portion 110. Figure 4 shows the cap portion 120 removed from the base portion 110. The cap portion 120 may be held in place by, for example, protrusions 123 on the inner surface fitting into recesses in the base portion (so-called claw engagement), or the cap portion 120 may be held to the base portion 110 by other holding means such as press-fitting, adhesive, or screws.

As shown in Figures 2 and 4, the microneedle 130 is provided on the end surface of the cap portion 120, with its tip exposed to the outside. When the fluid delivery device 100 is in use, the tip of the microneedle 130 is inserted through the epidermis of the biological tissue. This allows fluid to be injected from the fluid holding portion 140 into the biological tissue via the microneedle 130.

The fluid holding unit 140 is built into the cap unit 120 and holds the fluid to be supplied to the microneedles 130. The fluid holding unit 140 is preferably a water-absorbent body capable of soaking in liquid or gel-like medicinal solutions, but can be made of any material capable of holding fluid. Examples of water-absorbent bodies include sponge, gel, cotton, and the like. Examples of sponge materials include synthetic resins such as polyurethane and polyvinyl alcohol; natural polymers such as cellulose, and their derivatives. The fluid holding unit 140 may be built into the cap unit 120 surrounded by a tubular member 141 (sponge holder). This makes it easier to stabilize the posture and shape of the fluid holding unit 140 within the cap unit 120. Furthermore, when replacing the fluid holding unit 140, the entire tubular member 141 can be removed from the cap unit 120, making the replacement process easier.

The fluid holding portion 140 is positioned so as to come into contact with the electrode portion 111 when the cap portion 120 is attached to the base portion 110. The fluid holding portion 140 is flexibly deformable upon contact with the electrode portion 111. The fluid holding portion 140 may be provided with a hole or notch for inserting the electrode portion 111. The electrode portion 111 may have, for example, a first electrode 111a and a second electrode 111b, and the fluid holding portion 140 may have, for example, a first fluid holding portion 140a in contact with the first electrode 111a and a second fluid holding portion 140b in contact with the second electrode 111b.

The microneedle 130 may have a first microneedle 130a that delivers fluid from the first fluid holding portion 140a, and a second microneedle 130b that delivers fluid from the second fluid holding portion 140b.

An insulating wall 150 protruding from the cap portion may be provided between the first microneedle 130a and the second microneedle 130b. The tip of the insulating wall 150 may protrude further from the cap portion 120 than the microneedle 130. This prevents conduction between the first microneedle 130a and the second microneedle 130b without passing through biological tissue, thereby enhancing the effect of passing ionic current, medicinal solutions, etc. through biological tissue.

The insulating wall 150 may be configured to elastically deform when pressed against the biological tissue when the microneedle 130 is brought into contact with the biological tissue. In other words, the insulating wall 150 is preferably made of an elastic material such as silicone or rubber. This allows the microneedle 130 to be brought into contact with the biological tissue, allowing ionic current, medicinal solution, etc. to easily pass through the biological tissue, while maintaining the insulating effect of the insulating wall 150. The insulating wall 150 may be formed integrally with the cap portion 120. The insulating wall 150 is preferably made of a water-repellent material. This makes it difficult for medicinal solution delivered from the microneedle 130 to overcome the insulating wall 150 and reach the microneedle 130 on the opposite side, thereby enhancing the insulating effect. The insulating wall 150 is preferably formed in a ring shape so as to surround each microneedle 130.

The first fluid holding portion 140a and the second fluid holding portion 140b may be arranged in a first storage space 121a and a second storage space 121b, respectively, formed in the cap portion 120 (see Figure 4). The first storage space 121a and the second storage space 121b are recesses formed in the cap portion 120. The first storage space 121a and the second storage space 121b are separated by a wall 122 made of an insulating material. The first storage space 121a and the second storage space 121b are arranged such that, when the cap portion 120 is attached to the base portion 110 (attached state), the tip ends of the first electrode 111a and the second electrode 111b enter the first storage space 121a and the second storage space 121b, respectively. The first storage space 121a and the second storage space 121b each form a flow path communicating from the base portion 110 side to the microneedle 130 side. One end of the first storage space 121a and the second storage space 121b opens to the base portion 10 side, and the other end opens to the microneedle 130 side. In other words, one end of the first storage space 121a and the second storage space 121b is covered by the wall of the base portion 10 (the wall surface from which the electrode portion 111 protrudes), and the other end is covered by the first microneedle 130a and the second microneedle 130b, respectively.

The base unit 110 may include a gripping portion that is held by the user during use. The gripping portion is preferably shaped so that the user can hold it with one hand. The gripping portion may be rod-shaped extending in the left-right direction in FIGS. 1 and 3, or may be ball-shaped like a sphere. More specifically, the gripping portion may be pen-shaped, held like a pen, ball-grip-shaped, or brush-grip-shaped, held like a comb. The base unit 110 may also have a fastener such as a belt or band-shaped fastener for fastening to the head, neck, chest, abdomen, waist, buttocks, arms, wrists, legs, ankles, fingers, or toes, etc.

The fluid holding unit 140 may be configured to be replaceable by removing the cap unit 120 from the base unit 110. In this case, when the medicinal liquid in the fluid holding unit 140 runs out during use, it can be replaced with a fluid holding unit 140 containing new medicinal liquid. Note that the used cap unit 120 may be removed from the base unit 110 and the entire cap unit 120 replaced with a new one, or only the fluid holding unit 140 (or the set of the fluid holding unit 140 and the tubular member 141) may be replaced, or new medicinal liquid may be injected into the fluid holding unit 140 and allowed to soak in. In any case, even if the medicinal liquid in the fluid holding unit 140 runs out, the fluid delivery device 100 can be repeatedly used by replacing some parts.

When using the fluid delivery device 100, the microneedles 130 are pressed against biological tissue such as the scalp or other skin. This allows the microneedles 130 to penetrate the epidermis of the biological tissue and deliver a medicinal solution or the like into the biological tissue. When pressed against the biological tissue, the fluid delivery device 100 is energized and delivers the medicinal solution. The fluid delivery device 100 may be equipped with a notification means that uses this power. For example, the notification means may include a vibration device 160 that generates vibrations, a lighting unit that generates light, a speaker that generates sound, or a combination of these. When the microneedles 130 are pressed against the biological tissue and energized, power is supplied from the power source (battery 113) to the notification means. One or more of these notification means can easily notify the user that the medicinal solution or the like has been successfully injected. In this example, a vibration device 160 is provided that vibrates for a short period of time (e.g., 0.5 seconds, 1 second, etc.) to indicate the start of energization, making it easier for the user to understand that energization has begun. It is also possible to vibrate after a predetermined time has elapsed since energization began (e.g., 10 seconds, 30 seconds, 1 minute, 5 minutes, etc.) to notify the user when energization will end, or to vibrate briefly each time a predetermined time has elapsed to notify the user of the passage of time. Notification conditions such as vibration may be stored in the memory of a control device provided in the base unit 110 and controlled by the control processing unit.

As described above, the fluid delivery device 100 of this embodiment is a fluid delivery device that delivers fluid by bringing microneedles into contact with biological tissue, and includes a base portion having an electrode portion connected to a power supply means, a cap portion that is arranged to cover the electrode portion and is detachable from the base portion, the microneedle that is provided on the cap portion and has an exposed tip, and a fluid holding portion that is built into the cap portion and holds the fluid to be supplied to the microneedle, and is configured so that the fluid holding portion comes into contact with the electrode portion when the cap portion is attached to the base portion. This configuration allows for easy repeated use of the fluid delivery device.

The fluid delivery device 100 may be provided with a cover member that covers the cap portion 120. This can prevent fluid leakage through the microneedles 130 and prevent unintended contact with biological tissue. The cover member is preferably shaped to cover at least the entire surface on which the microneedles 130 are provided.

The cap portion 120 of the fluid delivery device 100 may have a transparent portion for visually checking the remaining amount of medicinal liquid or the like held in the fluid holding portion 140. The transparent portion may be made of, for example, a transparent or translucent resin. A transparent portion may be provided corresponding to each of the first fluid holding portion 140a and the second fluid holding portion 140b.

In this example, the microneedles 130 of the fluid delivery device 100 are automatically energized when pressed against biological tissue, but this is not limited to this. The base unit 110 may also be provided with a power switch for setting whether or not to energize. When the power switch is in the off position, it is possible to prevent current from being applied even when the microneedles 130 are pressed against biological tissue.

Figure 5 is a conceptual diagram illustrating the operating principle of a fluid delivery device. The device 10 in Figure 5 has a first transporter 11, a second transporter 12, a positive microneedle 13, a negative microneedle 14, and a current/voltage application means 15.

The first transport body 11 is elongated and has a first transport flow path (not shown) extending from one end to the other end on its interior. The first transport body 11 is configured to allow a first fluid 21 to flow through the first transport flow path. The second transport body 12 is elongated and has a second transport flow path (not shown) extending from one end to the other end on its interior. The second transport body 12 is configured to allow a second fluid 22 to flow through the second transport flow path. The first transport body 11 and the second transport body 12 may be configured separately from each other, or may be provided integrally.

The first fluid 21 flowed through the first transport channel and the second fluid 22 flowed through the second transport channel may be any fluid suitable for injection into a target object, but if the target object is skin or tissue inside a living body, it is preferable that each fluid contain a drug. The first fluid 21 and the second fluid 22 may be different fluids or the same fluid.

As shown in FIG. 6, the positive microneedle 13 and the negative microneedle 14 are each made of a porous material, have a conical shape, and have a flange portion 23 around the rear end of the base of the cone. The positive microneedle 13 has at least a first opening (not shown) at its tip and a first flow path (not shown) that has a fixed positive charge and is connected to the first opening. The negative microneedle 14 has at least a second opening (not shown) at its tip and a second flow path (not shown) that has a fixed negative charge and is connected to the second opening. The first flow path and the second flow path extend in a network-like manner through the voids in the porous material. In a specific example shown in FIG. 2, the height of the tip of the positive microneedle 13 and the negative microneedle 14 is 300 μm, and the height of the flange portion 23 is 300 μm. It is preferable to provide an elastically deformable insulating wall between the positive microneedle 13 and the negative microneedle 14 that is higher than the height of the microneedles.

As shown in FIG. 5 , the positive microneedle 13 is provided at one end of the first transporter 11 so that the first flow path communicates with the first transport flow path. The positive microneedle 13 is provided so that its tip protrudes from one end of the first transporter 11 in the extension direction of the first transporter 11. The negative microneedle 14 is provided at one end of the second transporter 12 so that the second flow path communicates with the second transport flow path. The negative microneedle 14 is provided so that its tip protrudes from one end of the second transporter 12 in the extension direction of the second transporter 12. The positive microneedle 13 and the negative microneedle 14 are adjacent to each other and are arranged so that their respective tips protrude on the same side.

The positive microneedle 13 and the negative microneedle 14 may each consist of a plurality of microneedles, as shown in FIG. 6, or may each consist of a single microneedle. If multiple microneedles are used, they may form a microneedle array. As shown in FIG. 2, the positive microneedle 13 and the negative microneedle 14 may each have a pointed tip so that they can be inserted into a target object and directly inject the first fluid 21 and the second fluid 22 into the target object. However, the tip may also be curved or flat so that they can spread the surface of the target object and allow the first fluid 21 and the second fluid 22 to penetrate into the target object. The first opening and the second opening may each consist of a single opening or multiple openings.

The positive microneedle 13 may be made of any material capable of immobilizing a positive charge in the first flow path, and the negative microneedle 14 may be made of any material capable of immobilizing a negative charge in the second flow path. The positive microneedle 13 and the negative microneedle 14 may be made of, for example, a hydrogel material, a porous resin, an oxide, a metal, or a biodegradable material. More specifically, the positive microneedle 13 may have a higher mobility of anions than cations when a fluid is introduced into the first flow path. For example, a positive charge may be immobilized on the wall surface of the first flow path, a positive charge may be embedded in the surface, or the positive microneedle 13 may be made of a hydrogel containing positively charged functional groups. The negative microneedle 14 may have a higher mobility of cations than anions when a fluid is introduced into the second flow path. For example, a negative charge may be immobilized on the wall surface of the second flow path, a negative charge may be embedded in the surface, or the negative microneedle 14 may be made of a hydrogel containing negatively charged functional groups.

Here, a hydrogel material refers to a material that forms a hydrogel when dispersed in water (dispersion medium). Examples of hydrogel materials include natural polymers such as agar, gelatin, agarose, xanthan gum, gellan gum, sclerotium gum, gum arabic, tragacanth gum, karaya gum, cellulose gum, tamarind gum, guar gum, locust bean gum, glucomannan, chitosan, carrageenan, quince seed, galactan, mannan, starch, dextrin, curdlan, casein, pectin, collagen, fibrin, peptides, chondroitin sulfates such as sodium chondroitin sulfate, hyaluronic acid (mucopolysaccharides) and hyaluronates such as sodium hyaluronate, alginic acid, alginate such as sodium alginate, and alginates such as calcium alginate, and derivatives thereof; cellulose derivatives such as methylcellulose, hydroxymethylcellulose, hydroxyethylcellulose, hydroxypropylcellulose, hydroxypropylmethylcellulose, and carboxymethylcellulose, and salts thereof; polyacrylic acid, polymethacrylic acid, poly(methylcellulose), ... Examples of suitable polymers include poly(meth)acrylic acids and salts thereof, such as sodium dimethacrylate and acrylic acid-alkyl methacrylate copolymers; synthetic polymers such as polyvinyl alcohol, polyhydroxyethyl methacrylate, polyacrylamide, poly(N-isopropylacrylamide), polyvinylpyrrolidone, polystyrene sulfonic acid, polyethylene glycol, carboxyvinyl polymers, alkyl-modified carboxyvinyl polymers, maleic anhydride copolymers, polyalkylene oxide resins, crosslinked products of poly(methyl vinyl ether-alt-maleic anhydride) and polyethylene glycol, crosslinked products of polyethylene glycol, N-vinylacetamide crosslinked products, acrylamide crosslinked products, and crosslinked products of starch-acrylate graft copolymers; silicones; interpenetrating network structure hydrogels and semi-interpenetrating network structure hydrogels; poly(2-hydroxyethyl methacrylate), poly(2-acrylamido-2-methylpropanesulfonic acid); and mixtures of two or more of these. Among these, from the viewpoints of load-bearing capacity and biocompatibility, preferred materials for forming the hydrogel are collagen, glucomannan; carboxymethylcellulose, sodium carboxymethylcellulose; polyacrylic acid, sodium polyacrylate; interpenetrating network structure hydrogels, and semi-interpenetrating network structure hydrogels. Furthermore, from the viewpoints of obtaining excellent mechanical strength and excellent biocompatibility, a crosslinked product of poly(methyl vinyl ether-alt-maleic anhydride) and polyethylene glycol is preferred, and further from the viewpoint of ensuring the electrical neutrality of the hydrogel, crosslinked polyethylene glycol is preferred.

Furthermore, examples of hydrogel materials with a fixed charge (positive or negative charge) include gel materials in which functional groups with a fixed charge have been introduced into hydrogel materials that do not have a fixed charge, and gel materials that are polymers containing monomer units with a fixed charge. Of these, gel materials that are polymers containing monomer units with a fixed charge are preferred, and copolymers of a non-charged monomer and a monomer with a fixed charge are more preferred.

Resins include polycarbonate, acrylonitrile-butadiene-styrene (ABS) resin, phenolic resin, acrylic resin, and methacrylic resin (such as polyglycidyl methacrylate resin). Oxides include inorganic oxides and their derivatives, such as silicon oxide, tin oxide, zirconia oxide, titanium oxide, niobium oxide, tantalum oxide, aluminum oxide, tungsten oxide, hafnium oxide, and zinc oxide. Metals include nickel, iron, and alloys thereof. Biodegradable materials include polylactic acid-glycolic acid copolymer (PLGA), PLGA-based composites, beta-tricalcium phosphate, calcium carbonate, polycaprolactone, polydioxanone, hydroxyapatite, polyethylene glycol, and magnesium alloys. The positive microneedle 13 and the negative microneedle 14 may be made of a combination of two or more of the materials listed above.

The current/voltage application means 15 has a first electrode 24 arranged in the first transport flow path and a second electrode 25 arranged in the second transport flow path, and is configured to be able to apply a current or voltage between the first electrode 24 and the second electrode 25. The first electrode 24 is inserted into the first transport flow path from the other end side of the first transport body 11, and the second electrode 25 is inserted into the second transport flow path from the other end side of the second transport body 12. More specifically, the current/voltage application means 15 is configured to apply a current or voltage with the first electrode 24 as negative and the second electrode 25 as positive. As a result, when a current or voltage is applied between the first electrode 24 and the second electrode 25 by the current/voltage application means 15, an ionic current flows through the first fluid 21 in the first flow path and the second fluid 22 in the second flow path, and electroosmotic flow causes the first fluid 21 to flow outward from the first opening, and the second fluid 22 to flow outward from the second opening.

Next, the operation will be described.
The fluid delivery device 10 is used as follows. First, the positive microneedle 13 provided at one end of the first transporter 11 and the negative microneedle 14 provided at one end of the second transporter 12 are inserted into or pressed against the skin or tissue inside a living body. In this state, a current or voltage is applied between the first electrode 24 and the second electrode 25 by the current/voltage application means 15. This causes an ionic current to flow through the first fluid 21 in the first flow path and the second fluid 22 in the second flow path, causing the first fluid 21 to flow outward from the first opening of the positive microneedle 13 and the second fluid 22 to flow outward from the second opening of the negative microneedle 14 due to electroosmotic flow. This allows the fluid delivery device 10 to directly inject the first fluid 21 and the second fluid 22 into the subcutaneous tissue or tissue. Therefore, by using fluids containing a drug as the first fluid 21 and the second fluid 22, the drug can be administered more efficiently than with conventional electroosmotic pumps that do not have microneedles.

The fluid delivery device 10 can control the flow rate of the generated electroosmotic flow by adjusting the current or voltage applied by the current/voltage application means 15, providing excellent control over the amount of discharge of the first fluid 21 and the second fluid 22. Furthermore, the fluid delivery device 10 has the positive microneedle 13 and the negative microneedle 14 adjacent to each other, with their respective tips protruding on the same side, allowing for a compact configuration and miniaturization of the entire device. Furthermore, the positive microneedle 13 and the negative microneedle 14 can be easily pierced or pressed against a target object simultaneously, making it easy to handle.

The microneedle may have a sharp tip as shown in Figure 5, or may have a blunt tip as shown in Figures 7 and 8. If the tip is blunt, it may have any shape as long as the tip is flat or formed with a smoothly curved surface, such as a truncated cone, truncated pyramid, columnar or rectangular pillar, or a dome-shaped tip.

As shown in Figure 8, when a blunt-tipped microneedle 130 (13, 14) is pressed against the skin, it can spread the stratum corneum 1, facilitating molecular permeation and allowing substances such as drugs held in the flow channel 11 to penetrate the stratum corneum 1. The microneedle 130 can also penetrate substances such as drugs into layer 2 below the stratum corneum 1. When pressed against the skin and an electric current or voltage is applied between the microneedle 130 and the skin, an ionic current flows, and the fixed charge in the flow channel 131 can generate an electroosmotic flow in the flow channel 131. This can increase the penetration efficiency of substances such as drugs. Furthermore, when the flow channel 131 is modified with a polymer, it can promote the movement of relatively large molecules or particles, for example, those with a molecular weight of approximately 500 to 10,000, thereby increasing the penetration efficiency of these molecules and particles.

The above describes in detail preferred embodiments of the present disclosure with reference to the accompanying drawings, but the technical scope of the present disclosure is not limited to such examples. It is clear that a person with ordinary skill in the technical field of the present disclosure could conceive of various modified or altered examples within the scope of the technical ideas set forth in the claims, and it is understood that these also naturally fall within the technical scope of the present disclosure.

Furthermore, the effects described in this specification are merely descriptive or exemplary and are not limiting. In other words, the technology disclosed herein may achieve other effects in addition to or in place of the above-mentioned effects that would be apparent to those skilled in the art from the description herein.

The following configurations also fall within the technical scope of the present disclosure.
(Item 1)
A fluid delivery device that delivers a fluid by bringing microneedles into contact with biological tissue,
a base portion having an electrode portion connected to a power supply means;
a cap portion disposed to cover the electrode portion and detachable from the base portion;
The microneedle is provided in the cap portion and has a tip exposed to the outside;
a fluid holding portion that is built into the cap portion and holds a fluid to be supplied to the microneedle;
Equipped with
The fluid delivery device is arranged so that the fluid holding portion contacts the electrode portion when the cap portion is attached to the base portion.
(Item 2)
the electrode portion has a first electrode and a second electrode,
Item 10. The fluid delivery device of item 1, wherein the fluid holding portion has a first fluid holding portion in contact with the first electrode and a second fluid holding portion in contact with the second electrode.
(Item 3)
The microneedle is
a first microneedle for delivering fluid from the first fluid holding portion;
Item 3. The fluid delivery device of item 2, comprising: a second microneedle for delivering fluid from the second fluid holding portion.
(Item 4)
4. The fluid delivery device according to claim 3, wherein an insulating wall protruding from the cap portion is provided between the first microneedle and the second microneedle.
(Item 5)
5. The fluid delivery device according to claim 4, wherein the tip of the insulating wall protrudes from the cap portion further than the microneedle.
(Item 6)
5. The fluid delivery device according to item 4, wherein the insulating wall is configured to be pressed against the biological tissue and elastically deformed when the microneedle is brought into contact with the biological tissue.
(Item 7)
Item 2. The fluid delivery device according to item 1, wherein the first fluid holding portion and the second fluid holding portion are respectively disposed in a first accommodating space and a second accommodating space formed in the cap portion.
(Item 8)
Item 10. The fluid delivery device of item 1, wherein the base portion includes a grip portion that is gripped by a user during use.
(Item 9)
Item 10. The fluid delivery device of item 1, wherein the fluid retaining portion is configured to be replaceable by removing the cap portion from the base portion.

100 Fluid delivery device 110 Base portion 111 Electrode portion 120 Cap portion 130 Microneedle 140 Fluid holding portion 150 Insulating wall

Claims (9)

A fluid delivery device that delivers a fluid by bringing microneedles into contact with biological tissue,
a base portion having an electrode portion connected to a power supply means;
a cap portion disposed to cover the electrode portion and detachable from the base portion;
The microneedle is provided in the cap portion and has a tip exposed to the outside;
a fluid holding portion that is built into the cap portion and holds a fluid to be supplied to the microneedle;
Equipped with
the cap is disposed so that the fluid holding portion is in contact with the electrode portion when the cap is attached to the base portion ;
the electrode portion has a first electrode and a second electrode,
the fluid holding portion has a first fluid holding portion in contact with the first electrode and a second fluid holding portion in contact with the second electrode,
The microneedle is
a first microneedle for delivering fluid from the first fluid holding portion;
a second microneedle for delivering fluid from the second fluid holding portion;
an insulating wall protruding from the cap portion is provided between the first microneedle and the second microneedle;
The fluid delivery device is configured such that when the microneedle is brought into contact with biological tissue, the insulating wall is pressed against the biological tissue and elastically deforms, thereby causing the microneedle to come into contact with the biological tissue. The fluid delivery device according to claim 1 , wherein a tip of the insulating wall protrudes from the cap portion further than the microneedle. The fluid delivery device of claim 1 , wherein the insulating wall is made of a water-repellent material . The fluid delivery device according to claim 3 , wherein the insulating wall is provided so as to surround the periphery of the first microneedle and the periphery of the second microneedle, respectively . The fluid delivery device according to claim 1 , wherein the fluid holding portion is a water-absorbent body that can absorb a liquid or gel-like fluid . a notification means for notifying that power supply from the power supply means has started;
The fluid delivery device according to claim 1 , wherein the energization is initiated by bringing the microneedles into contact with biological tissue, and power is supplied from the power supply means to the notification means . the first fluid holding portion and the second fluid holding portion are disposed in a first accommodating space and a second accommodating space formed in the cap portion , respectively;
The fluid delivery device of claim 1 , wherein the fluid retaining portion is configured to be replaceable by removing the cap portion from the base portion . The fluid delivery device of claim 1, wherein the base portion includes a grip portion that is gripped by a user during use. The fluid delivery device according to claim 6 , wherein the notification means notifies the user when energization has started, and also notifies the user when a predetermined time has elapsed since energization started .