EP4633717A1

EP4633717A1 - Ingestible device with dissolvable needle for improved gastric delivery

Info

Publication number: EP4633717A1
Application number: EP23844315.4A
Authority: EP
Inventors: Joseph DENNIS
Original assignee: Verily Life Sciences LLC
Current assignee: Verily Life Sciences LLC
Priority date: 2022-12-13
Filing date: 2023-12-12
Publication date: 2025-10-22
Also published as: AU2023397769A1; JP2026502345A; WO2024129666A1

Abstract

Introduced here is an ingestible device that is able to deliver medication directly into tissue along the gastrointestinal tract. Administration of a medication stored in the ingestible device can be effected by a combination of features. The ingestible device can include a plunging mechanism to which a needle is connected and a dissolvable trigger mechanism that holds the plunging mechanism in a first position. Following ingestion, the trigger mechanism may be exposed to body fluids to provoke dissolution. When the trigger mechanism dissolves, the plunging mechanism may move from the first position to a second position, thereby causing the needle to extend into tissue against which the ingestible device is lodged. Second, the needle may also be dissolved through exposure to body fluids, so as to ensure safe passage of the ingestible device through the gastrointestinal tract.

Description

INGESTIBLE DEVICE WITH DISSOLVABLE NEEDLE FOR IMPROVED GASTRIC DELIVERY

CROSS-REFERENCE TO RELATED APPLICATIONS

[0001] This application claims priority to US Provisional Application No. 63/387,266, titled “Ingestible Device with Dissolvable Needle for Improved Gastric Delivery” and filed on December 13, 2022, which is incorporated by reference herein in its entirety.

TECHNICAL FIELD

[0002] Various embodiments concern devices designed to administer medications while located inside of a living body and then pass through the living body through the gastrointestinal tract.

BACKGROUND

[0003] Pharmaceutical drugs (also called “medications”) are an important part of medicine that rely on the continual advancement of pharmacology to diagnose, cure, treat, or prevent disease. The term “administration” is commonly used to refer to the process by which an individual takes a medication. Medications are commonly designed for enteral administration - where the active ingredients enter the body via the gastrointestinal tract - as little oversight is needed. For example, many of the most common medications are intended to be orally administered, with dosages in tablet form, capsule form, or liquid form.

[0004] Medications having solid unit dosage forms - namely, tablets and capsules - have several benefits. Not only can medications be designed and/or manufactured to be easier to swallow but also to control the release rate of the active ingredients. Although oral consumption of medications in solid unit dosage form is a fairly straightforward route of administration, absorption of the active ingredients is a complex process.

[0005] Most medications that are orally administered are thought to be absorbed in the gastrointestinal tract via passive diffusion or active transport. Passive diffusion is widely considered the more important mechanism, and it depends on transfer of the active ingredients across the mucosa to the circulatory system down a concentration gradient. While transfer itself is largely dependent on the size of the concentration gradient, the rate at which transfer occurs can vary tremendously. For example, the transfer rate may depend on the molecular weight and size of the active ingredients, lipid solubility, mucosal blood flow, mucosal surface area, and mucosal permeability, among other variables. For this reason, it can be difficult to predict how quickly an orally administered medication will be absorbed by a living body.

BRIEF DESCRIPTION OF THE DRAWINGS

[0006] Figure 1 includes a cross-sectional view of an example of an ingestible device that is designed to administer medication as it travels through a living body, such as a human body or animal body.

[0007] Figure 2A illustrates the ingestible device prior to ingestion by a living body in its “storage state.”

[0008] Figure 2B illustrates the ingestible device in its “insertion state.”

[0009] Figure 2C illustrates the ingestible device in its “injection state.”

[0010] Figure 2D illustrates the ingestible device in its “passable state” following dissolution of the needle.

[0011] Figures 3A-D include simplified illustrations of the storage state, insertion state, injection state, and passable state, respectively.

[0012] Figure 4 illustrates several possible implementations of a trigger mechanism.

[0013] Figure 5 illustrates how, following ingestion through the mouth, an ingestible device can traverse the esophagus until settling within the stomach.

[0014] Figure 6 includes a timing diagram that illustrates - at a high level - how the dissolution rates of different components can compare to one another.

[0015] Various embodiments are shown in the drawings for the purpose of illustration. However, those skilled in the art will recognize that alternative embodiments may be employed without departing from the principles of the present disclosure. Accordingly, while certain embodiments are shown in shown in the drawings, the technologies described herein are amenable to various modifications. DETAILED DESCRIPTION

[0016] Contemporary research has begun exploring how to improve absorption of orally administered medications. For example, several entities have developed digital pills (also called “smart pills”) that are able to electromechanically effect administration of medications following ingestion. Digital pills commonly monitor aspects of the living body and then use this information to influence operations. The nature of this information can vary, however. For example, a digital pill could include a sensor that aids in the determination of location, and medication may not be administered until the output produced by the sensor indicates that the digital pill is located in a predetermined location.

[0017] Despite showing promise, digital pills are still susceptible to error. For example, erroneous output by the sensor could result in the medication being administered in an improper location. As another example, the electromechanical means used to effect administration may malfunction. Further, even if medication is administered in the proper location without issue, absorption still depends on passive diffusion - which, as noted above, can be difficult to predict with accuracy.

[0018] There are also some medications that are simply not suitable for oral administration. These medications may cause gastric irritation or experience inconsistent degradation, or these medications may simply be poorly absorbed within the gastrointestinal tract. Historically, many of these medications have been administered via injection. Such an approach has downsides, however, including the risk of infection from piercing the skin, the requirement for a sterile environment, and the like.

[0019] Introduced here is an ingestible device (also called a “pill”) that is able to address the aforementioned issues by delivering medication directly into tissue along the gastrointestinal tract. As further discussed below, administration of a medication stored in the ingestible device can be achieved by a combination of features.

[0020] First, the ingestible device can include an actuation mechanism that includes (i) a plunging mechanism to which a needle is connected and (ii) a dissolvable trigger mechanism that holds the plunging mechanism in a first position. The term “trigger mechanism” may be used to refer to a mechanical component that physically inhibits movement of the plunging mechanism (and therefore, administration of medication via the needle). Following ingestion, the trigger mechanism may be exposed to body fluids to provoke dissolution. When the trigger mechanism dissolves, the plunging mechanism may move from the first position to a second position, thereby causing the needle to extend into tissue against which the ingestible device is lodged. Such a feature allows the ingestible device to actuate at a predictable time - measured with respect to ingestion - without the need for external stimulus (e.g., a signal originating outside of the body) or internal stimulus (e.g., an output produced by a sensor).

[0021] Second, the needle may also be dissolved through exposure to body fluids. In operation, the bevel end of the needle may extend into tissue following dissolution of the trigger mechanism of the actuation mechanism. Over an interval of time, the medication in the ingestible device can be delivered into the tissue via the needle. The needle may be designed such that dissolution occurs after a predetermined amount of time has elapsed. The bevel end is sharp enough to pierce the tissue, and therefore, must be accommodated as the ingestible device traverses the gastrointestinal tract. Having the needle dissolve eliminates the need for the needle to be retracted back into the ingestible device in order to ensure safe passage through the gastrointestinal tract.

Terminology

[0022] References in the present disclosure to “an embodiment” or “some embodiments” means that the feature, function, structure, or characteristic being described is included in at least one embodiment. Occurrences of such phrases do not necessarily refer to the same embodiment, nor do they necessarily refer to alternative embodiments that are mutually exclusive of one another.

[0023] The term “based on” is to be construed in an inclusive sense rather than an exclusive sense. That is, in the sense of “including but not limited to.” Thus, the term “based on” is intended to mean “based at least in part on” unless otherwise noted.

[0024] The terms “connected,” “coupled,” and variants thereof are intended to include any connection or coupling between two or more elements, either direct or indirect. The connection or coupling can be physical, logical, or a combination thereof. For example, elements may be electrically or communicatively connected to one another despite not sharing a physical connection.

[0025] The term “module” may refer broadly to software, firmware, hardware, or combinations thereof. Modules are typically functional components that generate one or more outputs based on one or more inputs. A computer program may include or utilize one or more modules. For example, a computer program may utilize multiple modules that are responsible for completing different tasks, or a computer program may utilize a single module that is responsible for completing multiple tasks.

[0026] When used in reference to a list of items, the word “or” is intended to cover all of the following interpretations: any of the items in the list, all of the items in the list, and any combination of items in the list.

[0027] The term “biocompatible” means not harmful to living tissue. Accordingly, the term “biocompatible material” may be used to refer to any material that is not harmful to living tissue, whether its biocompatibility is presently known or not known.

[0028] The term “compressed state” may be used to refer to any state in which a spring is at least partially compressed. Meanwhile, the term “uncompressed state” may be used to refer to any state in which the spring is substantially uncompressed. Those skilled in the art will recognize that whether a spring is fully compressed or partially compressed while constrained - or fully uncompressed or substantially uncompressed while not constrained - may depend on the nature (e.g., design and size) of the spring.

Overview of Ingestible Device

[0029] Figure 1 includes a cross-sectional view of an example of an ingestible device 100 that is designed to administer medication as it travels through a living body, such as a human body or animal body. Note that Figure 1 and other illustrations in the present disclosure are not drawn to scale. Features may be shown significantly enlarged for greater clarity.

[0030] As shown in Figure 1 , the ingestible device 100 can include a capsule 102 with a cylindrical body 104 and atraumatically shaped ends 106A-B. One example of an atraumatically shaped end is a rounded shape that does not cause damage upon contacting living tissue, such as the roughly hemispherical ends shown in Figure 1 . This geometric shape is commonly called a “spherocylinder.” While the ingestible device 100 shown in Figure 1 has roughly hemispherical ends, the ingestible device 100 could have other atraumatically shaped ends in other embodiments. For example, at least one end of the capsule 102 may have a flat portion that can lie against the living tissue. The cylindrical body 104 and atraumatically shaped ends 106A-B may be referred to as the “structural components” of the capsule 102. To avoid contamination of an internal cavity defined by the cylindrical body 104 and/or the atraumatically shaped ends 106A-B, the structural components may be hermetically connected to one another.

[0031] Note that in some embodiments, the cylindrical body 104 is integrally formed with one of the atraumatically shaped ends. For example, the cylindrical body 104 may be integrally formed with atraumatically shaped end 106A, and therefore these structural components may not need to be connected to one another. Instead, components could be installed within these structural components and then atraumatically shaped end 106B may be connected thereto.

[0032] In some embodiments, these structural components comprise the same material. For example, these structural components may comprise plastic, metal, metal alloy, ceramic, polymer, or another biocompatible material, such as naturally derived materials that have comparable mechanical properties to plastics. In other embodiments, these structural components comprise different materials. For example, the atraumatically shaped end 106B through which the needle 108 extends may be comprised of a polymer or metal alloy, while the other atraumatically shaped end 106A and cylindrical body 104 may be comprised of plastic. A large disparity in weight may be helpful in ensuring that the ingestible device 100 is properly aligned with respect to the living tissue into which medication is to be injected, as further discussed below. Moreover, these structural components may have a coating that inhibits exposure to, and degradation from, body fluids. For example, these structural components may be coated with a polymer, a sugar, or a sugar alcohol, via a dip process or spray process, and the coating may improve safety, durability, or operational efficiency of the ingestible device 100. For example, a polymer coating can provide lubrication to aid in passage through the esophagus but may be chemically designed to denature, dissolve, or otherwise degrade in the stomach, yet still remain robust while in the mouth and esophagus and during normal handling.

[0033] Regardless of whether these structural components comprise the same material or different materials, the capsule 102 can be formed in various ways. For example, these structural components could be machined, injection molded, printed (e.g., with a three-dimensional printer), or otherwise formed to accommodate components of the ingestible device 100.

[0034] As shown in Figure 1 , atraumatically shaped end 106A may be largely or entirely empty to provide buoyancy. Here, for example, the inner surface of atraumatically shaped end 106A defines a cavity 1 10 that is vacant. However, relatively lightweight components could be situated within atraumatically shaped end 106A without meaningfully affecting the buoyancy. Such a design may cause the ingestible device 100 to naturally be oriented longitudinally when in body fluids, as further discussed below.

[0035] Meanwhile, a ballast 1 12 may be situated within atraumatically shaped end 106B. The ballast 112 may comprise any material that is able to provide stability. Examples of such materials include metals, metal alloys (e.g., stainless steel, titanium alloys, cobalt-chromium alloys), ceramics (e.g., tungsten carbide), and the like. In Figure 1 , the ballast 112 is connected to the longitudinal segment of the capsule 102 in such a manner that the ballast forms atraumatically shaped end 106B. In such embodiments, the ballast 1 12 is partially or entirely exposed to body fluids following ingestion of the ingestible device 100, and therefore may comprise a biocompatible material. However, in some embodiments, the ballast 1 12 is positioned inside atraumatically shaped end 106B. Because the ballast 1 12 is not exposed to body fluids in such embodiments, the ballast 112 may or may not comprise a biocompatible material.

[0036] As further discussed below, at least one of these structural components could comprise a dissolvable material. Assume, for example, that the capsule 102 includes atraumatically shaped end 106A and cylindrical body 104, but no atraumatically shaped end 106B (and therefore, the ballast 1 12 is exposed to body fluids). Atraumatically shaped end 106A and/or cylindrical body 104 may comprise a material that dissolves following exposure to body fluids for a predetermined amount of time. The material may be a water-soluble polymer or a mixture or combination of soluble and insoluble materials. Examples of soluble materials include polyethylene glycol (PEG), polyvinylpyrrolidone (PVP), Dextran, polyethylene oxide, polyvinyl alcohol (PVA), polyacrylic acid (PAA), hydroxypropyl methylcellulose (HPMC), etc. Examples of insoluble materials include polycarbonate, polystyrene, etc. Generally, the predetermined amount of time is sufficiently long that (i) a trigger mechanism 1 16 of an actuation mechanism 114 and (ii) the needle 108 dissolve before the predetermined amount of time elapses. Dissolution of atraumatically shaped end 106A, atraumatically shaped end 106B, or cylindrical body 104 may be helpful in decreasing the size of the ingestible device 100, making it easier for the ingestible device 100 to pass through the gastrointestinal tract after medication has been administered.

[0037] As shown in Figure 1 , atraumatically shaped end 106B can include an aperture 122 through which the needle 108 is able to extend. An actuation mechanism 114 may be responsible for moving the needle 108 from a first position in which its bevel end is located inside the capsule 102 to a second position in which its bevel end is located outside the capsule 102. As further discussed below, the actuation mechanism 114 may include a trigger mechanism 1 16 that, following ingestion, is exposed to body fluids through another aperture 124 in the capsule 102, a plunger mechanism 1 18 that is held in a first position by the trigger mechanism 1 16, and a spring 120 that is held in a compressed state by the plunger mechanism 1 18 while in the first position. The trigger mechanism 116 may comprise a material that dissolves following exposure to body fluids. Following dissolution of the trigger mechanism 1 16, the plunging mechanism 118 may move from the first position to a second position due to the spring 120 transitioning from the compressed state to an uncompressed state. The needle 108 may be connected - either directly or indirectly - to the plunger mechanism 118, and therefore movement of the plunger mechanism 118 may correspond to movement of the needle 108. The term “plunger mechanism” may be used to refer to a mechanical component that causes medication to be administer via rapid repositioning. Approaches to moving the needle 108 are discussed in greater detail below.

[0038] The capsule 102 may have any of a variety of different sizes, such as any of those sizes listed in Table I. Generally, the size of the capsule 102 depends on its contents (e.g., the amount of medication to be stored therein).

Table I: Example sizes of capsules.

[0039] Figures 2A-D illustrate an ingestible device 200 at different stages of administration.

[0040] Figure 2A illustrates the ingestible device 200 prior to ingestion by a living body. At this stage, the ingestible device 200 may be described as being in the “storage state.” As discussed above, the ingestible device 200 may comprise a capsule 202 having a central longitudinal axis 204 (or simply “central axis”) defined therethrough. The capsule 202 may have a substantially cylindrical segment that is interconnected between a pair of rounded ends. In embodiments where the rounded ends are in the form of hemispheres, this shape may be called a “spherocylinder.” Inside the substantially cylindrical segment, a reservoir 206 may store medication - generally in liquid form. The volume of medication that is storable in the reservoir 206 may depend on the size of the capsule 202. Generally, the reservoir 206 is able to store between 25-200 microliters (pL) (and preferably 50-100 pL). As shown in Figure 2A, the reservoir 206 may be partially defined by a seal 208. The bottom surface of the seal 208 - which may define a periphery of the reservoir 206 - may be roughly orthogonal to the central axis 204 while in a first position (also called an “upper position”).

[0041] A needle 210 may be arranged roughly along the central axis 204. The needle 210 may include a hollow shaft 212 with a port 214 defined therein and a bevel end 216. While the ingestible device 200 is shown as having a single port in Figures 2A-D, embodiments of the ingestible device 200 may have multiple ports (e.g., arranged circumferentially about the periphery of the needle 210) so that medication can be administered more quickly. Medication in the reservoir 206 may be able to enter the hollow shaft 212 through the port 214 and exit through the bevel end 216. In Figure 2A, the needle 210 is located in a first position corresponding to a storage state. When the needle 210 is located in the first position, the port 214 may be obscured so as to prevent medication from entering the hollow shaft 212. For example, the port 214 may be covered by the seal 208 through which the needle 210 extends, as shown in Figure 2A.

[0042] In Figures 2B-C, the bevel end 216 has a 45° regular bevel. However, the bevel end 216 could be designed otherwise depending on the tissue into which the needle 210 is to be inserted, the force with which the needle 210 will be inserted into the tissue, etc. Accordingly, the bevel end 216 could have a 22° bevel, 30° bevel, 35° bevel, 45° bevel, etc. In some embodiments, the end 216 may not be beveled at all, instead having a 90° blunt end. Moreover, the bevel end 216 could have a long bevel, medium bevel, short bevel, multi-bevel, or scalpel bevel. Further, the needle 210 could have other forms in some embodiments. For example, the ingestible device 200 could have multiple “microneedles” of relatively small size that are arranged in the form of an array, and the entire microneedle array could be actuated in accordance with the approach described herein. As another example, the ingestible device 200 could include a single needle, such as a macroneedle (e.g., comprised of epoxy), that has one or more apertures (also called “gills”) along its length through which medication can exit. As another example, the ingestible device 200 could include a barbed projection having one or more apertures through which medication can exit. These apertures may be arranged along its length or near its end (e.g., proximate to the barbs that embed into tissue to inhibit extraction). In such embodiments, the barbed projection may be dissolvable to ensure that the ingestible device 200 is able to readily detach from the tissue into which the medication is administered. Accordingly, the ingestible device 200 may be described as simply having a “projection” through which medication can be discharged into, or near, tissue.

[0043] As noted above, the ingestible device 200 may include an actuation mechanism that, in operation, causes the needle 210 to move along the central axis 204 from the first position in which the bevel end 216 is located inside the capsule 202 to a second position in which the bevel end 216 is located outside the capsule 202. The actuation mechanism can include (i) a trigger mechanism 218, (ii) a plunger mechanism 220, and (iii) a first spring 222. In embodiments where the ballast forms one of the atraumatically shaped ends, the ballast may have an aperture defined therethrough along the central axis 204, so as to accommodate actuation of the needle 210 along the central axis 204.

[0044] Following ingestion, the trigger mechanism 218 may be exposed to body fluids through an aperture (not shown) in the capsule 202. The trigger mechanism 218 can comprise a material that dissolves following exposure to the body fluids for a predetermined amount of time. The material could be a dissolvable polymer, for example. The trigger mechanism 218 could have various forms depending on the design of the actuation mechanism (and more specifically, the plunger mechanism 220 that is held in place by the trigger mechanism 218). In Figure 2A, for example, the trigger mechanism 218 is a pin that extends laterally through an opening (e.g., a hole or slot) in the plunger mechanism 220. The aperture in the capsule 202 through which body fluids are able to contact the trigger mechanism 218 could be located in nearly any position along the periphery of the capsule 202. For example, the aperture may be along the axial axis of the pin, such that the aperture is proximate to one end of the pin. As another example, the aperture may be along a radial axis of the pin, such that the aperture is centrally located along the length of the pin. More than one aperture may be defined through the capsule 202 if the trigger mechanism 218 is to be exposed to greater amounts of body fluid (e.g., to quicken dissolution). For example, the aperture may take the form of a slot that extends radially around at least part of the periphery of the capsule 202.

[0045] Further, the size of the trigger mechanism 218 may be altered to achieve dissolution at a desired rate. Generally, thinner trigger mechanisms will dissolve more quickly than thicker trigger mechanisms. The trigger mechanism 218 may have a diameter between 1 .0-2.5 millimeters. The length of the trigger mechanism 218 may depend on the size of the capsule 202. For example, the trigger mechanism 218 may have a length between 3.0-10.0 millimeters.

[0046] As shown in Figure 2A, the plunger mechanism 220 may initially be held in a first position by the trigger mechanism 218. While in the first position, the plunger mechanism 220 may hold the first spring 222 (also called the “insertion spring”) in a compressed state. The needle 210 can be connected to the plunger mechanism 220, and therefore, movement of the plunger mechanism 220 may correspond to movement of the needle 210 as further discussed below with reference to Figures 2B-C.

[0047] Another spring 224 (called the “second spring” or “injection spring”) can be interconnected between the plunger mechanism 220 and seal 208. When the plunger mechanism 220 in is the first position - shown in Figure 2A - the second spring 224 can be in an uncompressed state or lightly compressed state. When the second spring 224 is in an uncompressed state, the seal 208 will be suspended such that little or no pressure is applied to the medication in the reservoir 206. The tandem nature of the first and second springs 222, 224 may allow the medication to be stored in a low-pressure configuration. It also allows the insertion of the needle 210 into the tissue to be decoupled in time and force from the delivery of the medication into the tissue, allowing for more robust insertion and more reliable timing of medication delivery.

[0048] In some embodiments, a mucoadhesive disk 228 is secured along the end of the capsule 202 weighted by the ballast, as shown in Figure 2A. The term “mucoadhesion” is commonly used to refer to the adhesion that occurs between two surfaces, one of which is mucosal in nature. The mucoadhesive disk 228 may comprise any material that is able to improve, at least temporarily, adherence of the ingestible device 200 to the tissue into which medication is to be ejected. The mucoadhesive disk 228 may comprise a polymer, for example, that has hydrophilic groups (e.g., hydroxyl, carboxyl, amide, or sulfate) that attach to the tissue via interactions such as hydrogen bonding, hydrophobic interactions, or electrostatic interactions. For example, the polymer may be coated along the mucoadhesive disk 228, or the mucoadhesive disk 228 may be comprised entirely of the polymer. In some embodiments, the polymer is dissolvable. Dissolution of the polymer may allow the mucoadhesive disk 228 to more readily detach from the tissue. For example, adhesiveness could simply lessen due to dissolution of the polymer, or dissolution of the polymer could result in dissolution of the mucoadhesive disk 228 itself.

[0049] Referring now to Figure 2B, following dissolution of the trigger mechanism 218, the plunging mechanism 220 can move from the first position to a second position in response to the first spring 222 transitioning from the compressed state to an uncompressed state. In Figure 2B, dissolution of the trigger mechanism 218 causes the plunging mechanism 220 to move “downward” along the central axis 204. Because the needle 210 is connected to the plunging mechanism 220, movement of the plunging mechanism 220 can correspond to movement of the needle 210 along the central axis 204. Specifically, the bevel end 216 of the needle 210 can extend through another aperture 226 in the capsule 202. In the event that the ingestible device 200 is located adjacent to tissue, such movement of the needle 210 may result in the bevel end 216 piercing the surface of the tissue. Accordingly, Figure 2B illustrates the ingestible device 200 in its “insertion state.”

[0050] In Figure 2B, the needle 210 is located in a second position corresponding to an insertion state. When the needle 210 is located in the second position, the port 214 may be accessible such that medication can enter the hollow shaft 212. At a high level, the port 214 is located within the periphery of the reservoir 206 while the needle 210 is located in the second position. However, the needle 210 is preferably designed such that the port 214 is located near the “bottom” of the reservoir 206, as shown in Figure 2B. Medication may be able to more easily flow into the hollow shaft 212 when the port 214 is located nearer the “bottom” of the reservoir 206. Moreover, locating the port 214 near the “bottom” of the reservoir 206 will allow more medication to be administered, as the port 214 is less likely to be obscured, for example, by the seal 208 as it moves “downward” along the central axis 204 from the first position (also called the “upper position”) to a second position (also called a “lower position”). The seal 208 is located in the upper position in Figure 2A, while the seal 208 is located in the lower position in Figure 2C.

[0051] As shown in Figure 2B, the second spring 224 can be compressed due to “downward” movement of the plunging mechanism 220 along the central axis 204. This compression is due to the force applied to the bottom surface of the seal 208 by the medication stored in the reservoir 206. At a high level, the medication is sufficiently constrained (and therefore, pressurized) that force is applied against the bottom surface of the seal 208.

[0052] Referring now to Figure 2C, as medication flows into the needle 210 through the port 214 and out of the needle 210 through the bevel end 216, the amount of medication in the reservoir 206 will lessen (and therefore, the force applied against the bottom surface of the seal 208 will also lessen). Accordingly, Figure 2C illustrates the ingestible device 200 in its “injection state.” Over time, the second spring 224 will transition from the compressed state to an uncompressed state. Such movement will “push” the medication through the port 214 into the needle 210. Generally, the second spring 224 is designed such that when the second spring 224 returns to the uncompressed state, the seal 208 is located near the bottom of the reservoir 206, as shown in Figure 2C. Said another way, the second spring 224 may be designed - in combination with the seal 208, first spring 222 and plunger mechanism 220 - so that most, if not all, of the medication is administered into tissue through the bevel end 216 of the needle.

[0053] Note that, in operation, the insertion stage and injection stage shown in Figure 2B and Figure 2C, respectively, tend to occur in rapid succession. For example, the ingestible device 200 may only be in the insertion stage momentarily (e.g., several dozen or hundred milliseconds), as the second spring 224 rapidly compresses as shown in Figure 2B and then expands as shown in Figure 20.

[0054] As mentioned above, the needle 210 may comprise a material that dissolves following exposure to body fluids. In operation, the bevel end 216 of the needle 210 may extend into tissue during the insertion stage, and medication may flow through the bevel end 216 of the needle 210 into the tissue during the injection stage. The ingestible device 208 (and more specifically, its actuation mechanism, reservoir 206, seal 208, and needle 210) can be designed so that the medication is mostly, if not entirely, administered over an interval of time having a known length. For example, the interval of time may be several seconds to several minutes. As further discussed below, the needle 210 can be designed such that dissolution occurs after the interval of time has elapsed. Because the bevel end 216 is sharp enough to pierce the tissue, it must be accommodated if the ingestible device 200 will exit the living body by traversing the gastrointestinal tract. Having the needle 210 dissolve eliminates the need for the needle 210 to be retracted back into the capsule 202 in order to ensure safe passage through the gastrointestinal tract. Figure 2D illustrates the ingestible device 200 in its “passable state” following dissolution of the needle 210.

[0055] Figures 3A-D include simplified illustrations of the storage state, insertion state, injection state, and passable state, respectively. For simplicity, only the actuation mechanism - including the trigger mechanism 302, plunger mechanism 304, and first spring 306 - second spring 308, seal 310, and needle 312 are shown with respect to the capsule 300.

[0056] Following ingestion, the trigger mechanism 302 can be exposed to body fluids through an aperture in the capsule 300. The trigger mechanism 302 can hold the plunger mechanism 304 in a first position, and while the plunger mechanism 304 is in the first position, the plunger mechanism 304 may hold the first spring 306 in a compressed state, as shown in Figure 3A. Further, because the needle 312 is connected to the plunger mechanism 304, the trigger mechanism 302 can also hold the needle 312 in a first position - albeit indirectly via the plunger mechanism 304. While the needle 312 is in the first position, (i) the port through which medication enters can be obscured and (ii) the bevel end through which the medication exits can be fully retained within the capsule 300. For example, the port may be centrally located along the length of the needle 312, such that the port is covered by the seal 310.

[0057] As mentioned above, the trigger mechanism 302 can be comprised of a material that dissolves following exposure to body fluids. Following dissolution of the trigger mechanism 302, the plunger mechanism 304 can move from the first position to a second position, as shown in Figure 3B. Movement of the plunger mechanism 304 may be caused by the first spring 306 transitioning from the compressed state to an uncompressed state. Such action may cause the bevel end of the needle 312 to extend through an aperture in the capsule 300, as shown in Figure 3B. The stroke length of the needle 312 can depend on various factors, including the length of the needle 312, the length of the first spring 306, the amount of compression of the first spring 306, and the like. However, the length of the stroke during the insertion stage - commonly called the “insertion stroke” - may be between 2-5 millimeters (and preferably 2.5-3.5 millimeters).

[0058] As the plunger mechanism 304 moves toward the second position, the second spring 308 may become more compressed. Said another way, movement of the plunger mechanism 304 may cause the second spring 308 to transition from the uncompressed state to a compressed state. Note that the second spring 308 may not necessarily become fully compressed as shown in Figure 3B, but may instead be partially compressed due to the resistive force applied by the seal 310. Thereafter, the second spring 308 will transition from the compressed state back to the uncompressed state. As shown in Figure 3C, reversion of the second spring 308 to the uncompressed state can cause the seal 310 to move from a first position (Figure 3B) to a second position (Figure 3C). While not shown in detail here, the seal 310 may move through a reservoir 314, “pushing” medication in the reservoir 314 into the needle 312 through a port. The medication can travel through the hollow shaft of the needle 312 and then be ejected through the bevel end of the needle 312.

[0059] In some embodiments, movement of the seal 310 does not cause any further movement of the needle 312. Said another way, the stroke length of the needle 312 may not lengthen during the injection stage in some embodiments. However, in other embodiments, the needle 312 is further extended as the seal 310 moves. This may be caused by further movement of the plunger mechanism 304 as the reservoir is emptied of medication. The length of the stroke during the injection stage - commonly called the “injection stroke” - may be between 1-3 millimeters (and preferably 1 .5-2.0 millimeters). The injection stroke can be optimized based on the target volume of medication to be delivered and the configuration of the reservoir 314. For example, because a capsule of 000 size has a larger cross-sectional area available for the reservoir 314, less stroke may be required to deliver the same volume of medication in comparison to a capsule of 0 size.

[0060] The needle 312 can also be comprised of a material that dissolves, softens, or otherwise denatures following exposure to body fluids to reduce the potential for tissue damage while passing through the gastrointestinal tract. Accordingly, the needle 312 - or at least a portion thereof (e.g., the bevel end) - may dissolve. Generally, the needle 312 is designed or constructed such that sufficient time (e.g., 2-30 minutes, and preferably 5-10 minutes) elapses for administration purposes before dissolution begins. As shown in Figure 3D, dissolution of the needle 312 allows that end of the capsule 300 to become atraumatic once again.

[0061] Figure 4 illustrates several possible implementations of a trigger mechanism 402. Specifically, Figure 4 illustrates a “central design” where the trigger mechanism 402 extends into the plunger mechanism 404 and a “lateral design” where the trigger mechanism 402 runs alongside the plunger mechanism 404. Those skilled in the art will recognize that these implementations are intended to illustrate rather than limit the nature of the trigger mechanism 402.

[0062] In the “central design,” the trigger mechanism 402 can extend into an opening in the plunger mechanism 404. The opening could be a notch as shown in Figure 4, or the opening could be an aperture that extends entirely through the plunger mechanism 404 roughly along a latitudinal axis 408. When held in place by the trigger mechanism 402, the plunger mechanism 404 may be oriented lengthwise roughly along a longitudinal axis 406. As mentioned above, following ingestion, the trigger mechanism 402 may be exposed to body fluids through an aperture in the capsule 400, and upon dissolving, the plunger mechanism 404 may move “downward” along the longitudinal axis 406 such that the bevel end of the needle extends through the capsule 400.

[0063] In the “lateral design,” the trigger mechanism 402 can run alongside the plunger mechanism 404. As shown in Figure 4, the plunger mechanism 404 may be tilted (e.g., by 5-10 degrees with respect to the longitudinal axis 406), such that a latching component 410 engages a structural component 412. The structural component 412 may be partially complementary to the latching component 410, such that movement of the plunging mechanism 404 is inhibited by engagement between those components while the trigger mechanism 402 is in place. Generally, the latching component 410 and structural component 412 are designed to permit a maximum axial translation along the latitudinal axis 408 between 0.1-0.5 millimeters (and preferably about 0.2-0.3 millimeters). The structural component 412 could be affixed to the inner surface of the capsule 400, or the structural component 412 could be part of the capsule 400. For example, the structural component 412 may be representative of the inner surface of the cylindrical body (e.g., cylindrical body 104 of Figure 1 ) or atraumatically shaped end (e.g., atraumatically shaped end 106A of Figure 1 ). At a high level, the trigger mechanism 402 may “pin” the latching component 410 of the plunger mechanism 404 against the structural component 412. [0064] As shown in Figure 4, the trigger mechanism 402 may tip the plunger mechanism 404 off the longitudinal axis 406, and as the trigger mechanism 402 dissolves, the design of the plunger mechanism 404 (and more specifically, the latching component 410) may allow for self-alignment with the longitudinal axis 406 and release from its “pinned” position. Following dissolution of the trigger mechanism 402, diametric reduction of the structural component 412 may permit actuation of the plunger mechanism 404. The diametric reduction may vary based on the design (e.g., form and dimensions) of the latching component 410. For example, if the latching component 410 has a roughly inverted bell form, then diametric reduction of 0.3-0.7 millimeters may permit actuation. Following dissolution of the trigger mechanism 402, the plunger mechanism 404 may move “downward” along the longitudinal axis 406 and laterally along the latitudinal axis 408 toward the longitudinal axis 406. Accordingly, the plunger mechanism 404 may “straighten out” as it moves “downward.”

[0065] Having a dissolvable trigger mechanism may be an important feature of the ingestible device, as it allows actuation of the needle to be done “passively” in the sense that active actuation (e.g., with a motor) is not necessary. In the “lateral design,” while the trigger mechanism 402 prevents movement of the plunger mechanism 404 prior to dissolution, the trigger mechanism 402 need not be comprised of materials having high strength. Simply put, when the trigger mechanism 402 is positioned alongside the plunger mechanism 404, little material strength is required because this design eliminates dependence on reduction of shear strength. Further, the trigger mechanism 402 may be axi-symmetric with this design, which may ease the manufacturing and assembling processes.

Overview of Passive Locomotion and Dissolution Processes

[0066] Figure 5 illustrates how, following ingestion through the mouth, an ingestible device 500 can traverse the esophagus until settling within the stomach. Once inside the stomach, the ingestible device 500 can naturally situate itself in a longitudinal arrangement (also called the “vertical arrangement”). The ingestible device 500 may have a central axis 502 defined therethrough, and when the ingestible device 500 is in the vertical arrangement, the central axis 502 may be roughly orthogonal to the surface 504 of the tissue into which medication is to be injected.

[0067] As mentioned above, the ingestible device 500 may naturally situate itself in the vertical arrangement along the bottom of the stomach. Generally, this is accomplished by designing a first end (e.g., atraumatically shaped end 106A of Figure 1 ) of the ingestible device 500 to provide buoyancy and a second end (e.g., atraumatically shaped end 106B of Figure 1 ) of the ingestible device 500 to provide ballast. For example, the first end may be largely or entirely empty to provide buoyancy, while the second end may include a high-density component (e.g., comprised of metal, metal alloy, ceramic, etc.) that ensures proper orientation within the stomach.

[0068] In some embodiments, a mucoadhesive is coated along at least the second end of the ingestible device 500. Said another way, the mucoadhesive may be coated along at least an exterior surface of one end of the ingestible device 500. Like the mucoadhesive disk 228 of Figures 2A-D, the mucoadhesive coating can adhere the ingestible device 500 to the tissue to ensure more reliable delivery of the medication contained in the ingestible device 500. The mucoadhesive coating may comprise a polymer, for example, that has hydrophilic groups (e.g., hydroxyl, carboxyl, amide, or sulfate) that attach to the tissue via interactions such as hydrogen bonding, hydrophobic interactions, or electrostatic interactions. Note that in some embodiments, the mucoadhesive coating is constructed or applied such that adhesiveness decreases over time. Assume, for example, that the ingestible device 500 is designed such that its needle dissolves following a first interval of time. It may be desirable for the mucoadhesive coating to lose adhesiveness after - or shortly before - expiration of the first interval of time, so that the ingestible device 500 more readily detaches from the surface 504 of the tissue. Accordingly, the mucoadhesive coating may be designed to dissolve, allowing the ingestible device 500 to complete transit through the gastrointestinal tract intact.

[0069] Such an approach to gastric delivery of medication may be preferable to traditional medications with solid unit dosage forms that rely heavily on passive diffusion. For example, esophageal transit time of the ingestible device 500 may be 5 minutes or less following ingestion and medication may be administered shortly thereafter (e.g., within 5-20 minutes of ingestion, and preferably within 5- 10 minutes of ingestion), while traditional medications may not be absorbed for 120 minutes or more. Consequently, medications can be administered - and take effect - more quickly using the ingestible device introduced here. There is also improved safety margin by administering medication in the stomach, as the thickness of gastric tissue generally averages about 5 millimeters in comparison to intestinal tissue that generally averages about 1 millimeter.

[0070] Figure 6 includes a timing diagram that illustrates - at a high level - how the dissolution rates of different components can compare to one another. As mentioned above, various components of an ingestible device 600 can be comprised of dissolvable materials. For example, a trigger mechanism 602 could be at least partially comprised of a first dissolvable material, and a needle 604 could be at least partially comprised of a second dissolvable material. Further, the capsule 606 could be at least partially comprised of a third dissolvable material. For example, any combination of the cylindrical body (e.g., cylindrical body 104 of Figure 1 ) and atraumatically shaped ends (e.g., atraumatically shaped ends 106A-B of Figure 1 ) may comprise the third dissolvable material.

[0071] The first dissolvable material may be selected, produced, or manufactured (e.g., in the form of the trigger mechanism 602) so as to dissolve at a first roughly known rate. Because the rate at which the first dissolvable material dissolves is predictable, the total time that it takes for the trigger mechanism 602 to dissolve may also be predictable. For example, the trigger mechanism 602 may be designed, manufactured, and installed within the capsule 606 such that dissolution takes between 2-20 minutes (and preferably 5-10 minutes). Preferably, the first roughly known rate should be fast enough that medication can be promptly administered but slow enough that sufficient time elapses for the ingestible device 600 to reach the preferred organ (e.g., the stomach) before meaningful dissolution occurs. The first dissolvable material should have sufficient flexural strength to hold the compressed spring in place and dissolves quickly upon exposure to liquid. Preferably, the first dissolvable material should also be easy to fabricate for scale up. For example, the first dissolvable material may be a sugar alcohol, such as sorbitol or isomalt, zein protein, PEG, or PVP. The mechanical properties and dissolution rate of a trigger mechanism 602 comprised of sugar alcohol may be “tuned” by mixing with an additive, such as talc or PVP powder, or coating with a thin polymer-based moisture barrier layer. Other water soluble materials such as polyvinyl alcohol (PVA), butene-diol vinyl alcohol copolymer (BVOH), or blends may also be used to slow down dissolution rate.

[0072] The second dissolvable material may be selected, produced, or manufactured (e.g., in the form of the needle 604) so as to dissolve at a second roughly known rate. Because the rate at which the second dissolvable material dissolves is predictable, the total time that it takes for the needle 604 to dissolve may also be predictable. For example, the needle 604 may be designed, manufactured, and installed within the capsule 606 such that dissolution takes between 2-30 minutes (and preferably 5-10 minutes). Note that because the needle 604 is initially housed within the capsule 606, dissolution may not begin until the needle 604 extends outside of the capsule 606. Therefore, dissolution of the needle 604 may occur 4-50 minutes (and preferably 10-20 minutes) following ingestion of the ingestible device 600. The second dissolvable material could be zein protein, PVP, PEG, or a combination thereof. Other biodegradable polymers such as polylactic acid (PLA), polyglycolic acid (PGA), poly(lactide-co- glycolide), and water-soluble materials, such as Dextran, sugar alcohol, and the like, may also be used in the different combinations. [0073] As mentioned above, only a portion of the needle 604 may comprise the second dissolvable material. Assume, for example, that the needle 604 is designed such that only its bevel end extends through an end of the capsule 606 during the insertion and injection stages. In such a scenario, only the bevel end may comprise the second dissolvable material, as further dissolution of the needle 604 is not necessary for the end to become atraumatic once again.

[0074] As mentioned above, the needle 604 may have a centrally located port through which medication is able to flow, and this centrally located port may initially be obstructed (e.g., by the seal) to prevent entry of medication before the ingestible device 600 is properly lodged against tissue. This design allows the medication to be separated from the needle 604 in storage. When the needle 604 is inserted into the tissue, the port can transition, for example, from within the seal to a location near the bottom of the reservoir. This motion opens the lumen of the needle 604 to the medication and allows the medication to be dispensed. Until such time as the port is exposed to the medication, there is no path for dispensing, and therefore the reservoir can remain sealed.

[0075] The third dissolvable material may be selected, produced, or manufactured (e.g., in the form of the capsule 606) so as to dissolve at a third roughly known rate that is slower than the first and second roughly known rates. Because the rate at which the third dissolvable material dissolves is predictable, the total time that it takes for the capsule 606 - or at least a portion thereof - to dissolve may also be predictable. For example, the capsule 606 may be designed or manufactured such that dissolution takes between 20-75 minutes (and preferably 30-50 minutes). The third dissolvable material could be a plastic material such as polycarbonate or polystyrene, a water-soluble material such as polyethylene oxide (e.g., Polyox™), or a combination thereof.

[0076] Like the trigger mechanism 602, the capsule 606 will be immediately exposed to body fluids following ingestion. To ensure that medication is properly administered, the third roughly known rate is generally slower than the first roughly known rate by at least a predetermined amount. For example, the needle 604 may dissolve in about 10, 25, 40, or 50 percent of the time that it takes for the capsule 606 to dissolve. The second roughly known rate could be slower than the first roughly known rate, or the second roughly known rate could be faster than the first roughly known rate. At a high level, the second roughly known rate may depend on how quickly the medication is expected to be administered. Preferably, the needle 604 should not meaningfully dissolve until at least a predetermined amount (e.g., 80, 90, 95, or 98 percent) of the medication has been administered into the tissue. The term “meaningfully dissolve” may be used to refer to the stage at which the structural integrity of a component is impacted by dissolution.

[0077] Note that in some embodiments, the capsule 606 may have a mucoadhesive coating 608 applied thereto. The mucoadhesive coating 608 may comprise any material that is able to improve, at least temporarily, adherence of the ingestible device 600 to the tissue into which medication is to be ejected. In some embodiments, the mucoadhesive material is also dissolvable. Dissolution of the mucoadhesive material may be helpful in ensuring that the ingestible device 600 readily detaches from the tissue. The mucoadhesive material may be comprised of a material that takes between 20-75 minutes (and preferably 30-50 minutes) to dissolve. Thus, the mucoadhesive material may dissolve at roughly the same rate as the capsule 606. In some embodiments the mucoadhesive material dissolves at a faster rate than the capsule 606, while in other embodiments the mucoadhesive material dissolves at a slower rate than the capsule 606.

[0078] The rates at which the trigger mechanism 602, needle 604, capsule 606, and mucoadhesive coating 608 dissolve can vary based on, for example, the amount of time over which medication is expected to be administered. This amount of time may vary based on the quantity of medication stored in the ingestible device 600, the viscosity of medication stored in the ingestible device 600, the nature of the springs and seal that effect administration, etc. While the rates may vary, the general relationship between the rates may be predictable. Generally, the trigger mechanism 602 dissolves at the fastest rate. In embodiments where the capsule 606 includes a mucoadhesive coating 608, the mucoadhesive coating 608 may dissolve at a faster rate than the needle 604 (i.e., so that the needle 604 can be exposed to body fluids shortly after medication has been administered), a slower rate than the needle 604 (i.e., so that the needle can degrade, at least partially, before the ingestible device 600 dislodges from the tissue), or a similar rate as the needle 604. Meanwhile, the capsule 606 may dissolve at the slowest rate, so as to ensure that the insertion and injection stages have been fully completed before the capsule 606 begins dissolving.

Remarks

[0079] The foregoing description of various embodiments of the claimed subject matter has been provided for the purposes of illustration and description. It is not intended to be exhaustive or to limit the claimed subject matter to the precise forms disclosed. Many modifications and variations will be apparent to one skilled in the art. Embodiments were chosen and described in order to best describe the principles of the invention and its practical applications, thereby enabling those skilled in the relevant art to understand the claimed subject matter, the various embodiments, and the various modifications that are suited to the particular uses contemplated.

[0080] Although the Detailed Description describes certain embodiments and the best mode contemplated, the technology can be practiced in many ways no matter how detailed the Detailed Description appears. Embodiments can vary considerably in their implementation details, while still being encompassed by the specification. Particular terminology used when describing certain features or aspects of various embodiments should not be taken to imply that the terminology is being redefined herein to be restricted to any specific characteristics, features, or aspects of the technology with which that terminology is associated. In general, the terms used in the following claims should not be construed to limit the technology to the specific embodiments disclosed in the specification, unless those terms are explicitly defined herein. Accordingly, the actual scope of the technology encompasses not only the disclosed embodiments, but also all equivalent ways of practicing or implementing the embodiments.

[0081] The language used in the specification has been principally selected for readability and instructional purposes. It may not have been selected to delineate or circumscribe the subject matter. It is therefore intended that the scope of the technology be limited not by this Detailed Description, but rather by any claims that issue on an application based hereon. Accordingly, the disclosure of various embodiments is intended to be illustrative, but not limiting, of the scope of the technology as set forth in the following claims.

Claims

CLAIMS What is claimed is:

1 . A device designed for ingestion by a living body, the device comprising: a capsule having a central axis defined therethrough; a reservoir in which medication is stored in liquid form, wherein the reservoir is at least partially defined by a seal that is roughly orthogonal to the central axis while in a first position; a trigger mechanism that, following ingestion, is exposed to body fluids through a first aperture in the capsule, wherein the trigger mechanism comprises a first material that dissolves following exposure to the body fluids for a first amount of time; a plunger mechanism that is held in a first position by the trigger mechanism; a projection that is connected to the plunger mechanism and fully retained within the capsule when the plunger mechanism is in the first position, wherein the projection has a port through which the medication is able to enter and a bevel end through which the medication is able to exit, and wherein the projection comprises a second material that dissolves following exposure to the body fluids for a second amount of time that is greater than the first amount of time; a first spring that is held in a compressed state by the plunger mechanism while in the first position; and a second spring that is interconnected between the plunger mechanism and the seal in an uncompressed state; wherein following dissolution of the trigger mechanism, the plunger mechanism moves from the first position to a second position due to the first spring transitioning from the compressed state to an uncompressed state, thereby causing

(i) the bevel end of the projection to extend through a second aperture in the capsule and into body tissue, and

(ii) the second spring to transition from the uncompressed state to a compressed state, and the seal moves from the first position to a second position due to the second spring transitioning from the compressed state back to the uncompressed state, thereby causing the medication to enter the projection through the port and exit through the bevel end; and wherein following dissolution of the projection, the capsule dislodges from the body tissue for traversal through the living body.

2. The device of claim 1 , wherein the capsule has a substantially cylindrical segment that is interconnected between a first rounded segment and a second rounded segment.

3. The device of claim 2, further comprising: a ballast that is positioned inside the first rounded segment, wherein the ballast causes the capsule to be naturally positioned in a vertical orientation while in the body fluids, with the central axis roughly orthogonal to a surface of the body tissue.

4. The device of claim 3, wherein the second rounded segment is largely or entirely empty to provide buoyancy.

5. The device of claim 1 , wherein the port of the projection is shielded by the seal when the plunger mechanism is in the first position.

6. The device of claim 1 , wherein the projection comprises a second material that dissolves following exposure to the body fluids for a second amount of time that is longer than the first amount of time.

7. The device of claim 1 , wherein the trigger mechanism is positioned laterally alongside a latch of the plunger mechanism, and wherein when the plunger mechanism is held in the first position, the latch is laterally offset from the central axis such that the latch engages a structural feature along an interior surface of the capsule.

8. A device designed for ingestion by a living body, the device comprising: a capsule having a central axis defined therethrough; a needle that comprises a material that dissolves following exposure to body fluids for a predetermined amount of time, wherein the needle comprises

(i) a hollow shaft with a port through which medication in the capsule is able to enter, and

(ii) a bevel end through which the medication is able to exit; and an actuation mechanism that, in operation, causes the needle to move along the central axis from a first position in which the bevel end is located inside the capsule to a second position in which the bevel end is located outside the capsule.

9. The device of claim 8, wherein the actuation mechanism comprises: a trigger mechanism that, following ingestion, is exposed to body fluids through a first aperture in the capsule, wherein the trigger mechanism comprises a second material that dissolves following exposure to the body fluids for a second predetermined amount of time, a plunger mechanism to which the needle is connected, wherein the plunger mechanism is held in a first position by the trigger mechanism, and a spring that is held in a compressed state by the plunger mechanism while in the first position.

10. The device of claim 9, wherein following dissolution of the trigger mechanism, the plunger mechanism moves from the first position to a second position due to the spring transitioning from the compressed state to an uncompressed state, thereby causing the bevel end to extend through a second aperture in the capsule.

1 1 . The device of claim 9, wherein the second predetermined amount of time is between 5 minutes and 20 minutes.

12. The device of claim 11 , wherein the predetermined amount of time is between 20 minutes and 60 minutes.

13. The device of claim 9, further comprising: a reservoir in which the medication is stored, wherein the reservoir is at least partially defined by a seal that is roughly orthogonal to the central axis while in a first position.

14. The device of claim 13, further comprising: a spring that is interconnected between the actuation mechanism and the seal in an uncompressed state.

15. The device of claim 14, wherein when the actuation mechanism is actuated, the seal moves along the central axis toward an end of the capsule through which the bevel end of the needle extends, thereby pressurizing the medication in the reservoir.

16. The device of claim 9, wherein the capsule has a substantially cylindrical segment that is interconnected between a first rounded segment and a second rounded segment, and wherein the device further comprises: a mucoadhesive that is coated on at least an exterior surface of the first rounded segment of the capsule.

17. The device of claim 16, further comprising: a ballast that is positioned inside the first rounded segment of the capsule, wherein the ballast causes the capsule to be naturally positioned in a vertical orientation while in the body fluids, with the central axis roughly orthogonal to a surface of body tissue into which the bevel end extends when the actuation mechanism is actuated.

18. A device designed for ingestion by a living body, the device comprising: a capsule that includes a reservoir of medication; a needle that has a bevel end through which the medication is able to exit, wherein the needle is extendable through a first aperture in the capsule; and an actuation mechanism that includes - a plunger mechanism to which the needle is connected, and a trigger mechanism that holds the plunger mechanism in a first position and, following ingestion, is exposed to body fluids through a second aperture in the capsule; wherein the trigger mechanism comprises a first material that dissolves following exposure to the body fluids for a first amount of time, thereby permitting the plunger mechanism to move from the first position to a second position so as to cause the needle to extend through the first aperture in the capsule; and wherein the needle comprises a second material that dissolves following exposure to the body fluids for a second amount of time that is greater than the first amount of time.

19. The device of claim 18, wherein at least part of the capsule comprises a third material that dissolves following exposure to the body fluids for a third amount of time that is greater than the first and second amounts of time.

20. The device of claim 18, wherein the needle has a total stroke length of between 2 millimeters and 5 millimeters.