INFUSION PUMP FLOW CONTROL

Abstract

The present invention relates to methods and systems for infusing a user. An infusion pump includes a housing with an elastic component configured to expand and store potential energy. The infusion pump includes a first tube fluidly coupled to an outlet of the housing. The first tube is configured to conduct fluid from the housing at a first flow rate. The infusion pump includes an air filter fluidly coupled to a distal end of the first tube by means of an air filter inlet. The infusion pump includes a second tube fluidly coupled to an air filter by means of an air filter outlet. The second tube is configured to adjust the first flow rate of the fluid conducted from the housing to a second flow rate.The infusion pump also includes one or more components for distributing the fluid to a user, one or more components seamlessly coupled to an outlet of the second tube.

Description

INFUSION PUMP FLOW CONTROL Field of Invention The present description relates to fluid pumps. More particularly, it relates to portable infusion pumps that are useful for pumping relatively small quantities of fluids under substantially constant pressure at precise and constant flow rates over an extended period of time. The present invention is particularly useful, but not exclusively, for single use as a disposable pump for infusing fluid medications to an outpatient. Background of the Invention Disposable pumps (also called elastomeric pumps, ambulatory pumps, or CADD pumps) have been around for some time. These disposable pumps offer clear advantages in low-cost care and are used in a variety of applications, from antibiotic administration and pain management to, and including, chemotherapy delivery. Alternative-site care (e.g., at home or in large oncology clinics) is also becoming more common. Given the rising costs of healthcare, more non-acute options are needed. Disposable pumps can provide users with a cost-effective way to meet their healthcare needs. However, current disposable pumps cannot always RfrCfr Ln / Zznz / E / YIAI Ref. 340301 to provide precise and constant flow rates for infusing a fluid medication to a user. Therefore, those skilled in the art have recognized the need for disposable pumps capable of delivering a fluid medication at a precise and constant flow rate. Another identified need is for a flow restrictor that can be manufactured more cost-effectively and that can utilize interchangeable parts with restrictors of different sizes. The invention satisfies these and other needs. Brief Description of the Invention In some implementations, an infusion pump includes a housing. The housing includes an elastic component configured to expand and store potential energy generated by the fluid within the infusion pump. The infusion pump includes a first tube fluid-coupled to an outlet of the housing. The first tube is configured to conduct fluid from the housing at a first flow rate based, in part, on the potential energy stored by the elastic component. The infusion pump includes an air filter fluid-coupled to a distal end of the first tube via an air filter inlet. The air filter is configured to expel air from the fluid, through one or more air outlets, substantially upstream, so that the fluid exiting the air filter is primed without RfrCfr ίη / ZZΖΠZ / E / YΙΛΙ air. The infusion pump includes a second fluid-coupled tube to the air filter via an outlet in the air filter configured to adjust the first flow rate of the fluid delivered from the housing, through the first tube, to a second flow rate. The second flow rate is based, at least in part, on an inside diameter of the second tub. The infusion pump further includes an outlet from the second fluid-coupled tube to one or more components for distributing the fluid to a user. In some implementations, a method of fluid infusion to a patient is performed using an infusion pump. The infusion pump includes a housing with an elastic component, a first tube fluidly coupled to the housing via an outlet, an air filter fluidly coupled to a distal end of the first tube via an air filter inlet, a second tube fluidly coupled to the air filter via an air filter outlet, and an outlet from the second tube fluidly coupled to one or more components.In some implementations, the method performed in the infusion pump includes expanding the elastic component with the fluid to store potential energy generated by the fluid within the infusion pump; directing fluid from the housing through the first tube at a first flow rate based, in part, on the potential energy stored by the elastic component; expelling air from the fluid through one or more air filter vent holes, where the air is expelled substantially upstream, so that the fluid leaving the air filter is primed without air; adjusting the first flow rate of the fluid directed from the housing, through the first tube, to a second flow rate, the second flow rate being based, at least in part, on an inside diameter of the second tube; and distributing the fluid to a user through one or more components coupled to the outlet of the second tube. Brief Description of the Figures For a better understanding of the various implementations described, please refer to the Implementation Descriptions below, along with the following figures. Similar reference numbers refer to corresponding sections throughout the figures and descriptions. Figure 1 illustrates a disposable infusion pump, according to some implementations. Figure 2 illustrates a disposable infusion pump, according to some implementations. Figure 3 is an overview of the disposable pump system, according to some implementations. Figures 4A and 4B illustrate cross-sectional views of the disposable pump, according to some implementations. RfrCfr ίη / ΖΖΠΖ / Ε / ΥΙΛΙ Figures 5A and 5B illustrate a flow restriction component, according to some implementations. Figures 6A and 6B illustrate another flow restriction component, according to some implementations. Figure 7 is a block diagram representing a flow controller, according to some implementations. Figures 8A-8D are flow diagrams illustrating a method for controlling the flow rate of the disposable pump, according to some implementations. Detailed Description of the Invention The implementations described herein include an infusion pump and infusion methods for delivering a fluid medication to a user. The infusion pump is attached to a user and configured to deliver the fluid medication to the user at a precise and constant flow rate. Accordingly, the implementations described herein provide various devices and / or techniques for controlling and / or adjusting the flow rate of the fluid medication. Furthermore, by delivering the fluid medication to a user at precise and constant flow rates that can be controlled, the infusion pump and infusion methods described herein facilitate the safe infusion of the fluid medication. Some additional advantages of implementations consistent with this description include control RfrCfr Ln / Zznz / E / YIAI Precise flow rates and the lowest achievable flow rates for the fluid medication delivered to a user. In particular, the infusion pump can be designed to produce the desired flow rate and, if necessary, can precisely adjust the flow rate as required. Furthermore, the infusion pump and infusion methods allow for considerable flexibility in achieving different flow rates using one or more of the techniques and / or devices described herein. The implementations described herein are suitable for a variety of fluid medications and / or applications (e.g., chemotherapy administration, antibiotic administration, pain management, etc.).Consequently, improving flexibility in adjusting flow rates and / or increasing the number of applications of infusible pumps reduces overall costs by providing an affordable alternative for infusing fluid medications that is functional in a variety of applications. Figure 1 illustrates a disposable infusion pump according to several implementations. As shown in Figure 1, user 102 can carry the disposable pump 100 (also called an infusion pump) while ambulating, and it can be attached to user 102 by the support 104. The support 104 can be a belt, waist pack, lanyard, backpack, bag, and / or other device for carrying the disposable pump 100. Furthermore, Figure 1 shows that the pump The disposable infusion set RfrCfr Ln / Zznz / E / YIAI 100 can be seamlessly coupled to the user 102 for fluid infusion into the user 102 via a first medical tube 106. In some implementations, the fluid may be water or any fluid medication, such as chemotherapy drugs, analgesics, prescription medications, saline solution, etc. The first medical tube 106 can be any type of IV tubing for infusion, such as micro-bore intravenous tubing with an air filter, small-bore intravenous tubing, large-bore intravenous tubing, and / or any other type of infusion tubing. In some implementations, the material for the first 106 medical tubing is Tygon®, thermoplastic elastomers (TPE), polyethylene, polyvinyl chloride (PVC), nylon, silicone, and / or other similar materials. Tygon is bonded to the various components of the infusion pump with a single solvent application. Tygon offers the advantage of being able to be extruded to a significantly smaller internal diameter than other tubing types (e.g., PVC) within the pump, improving flow rate accuracy and making the tubing much less sensitive to length adjustments. Furthermore, a small change in diameter accuracy can have an exponential impact on rate accuracy. In some implementations, an in-line air filter RfrCfr Ln / Zznz / E / YIAI 108 seamlessly connects to the first medical tubing 106 (via an inline air filter inlet 108). The inline air filter 108 can be a pediatric filter IV, a microfilter IV, and / or other filters suitable for drug administration, chemotherapy, insulin infusion, antibiotic therapy, lipid / PNT infusion, neonatal infusion therapy, etc. The inline air filter 108 is configured to remove air from the delivered fluid (e.g., by leaving the disposable pump 100) to prevent air infusion to the user 102. In some implementations, the inline air filter 108 is configured to remove contaminants and / or particles from the fluid to prevent the infusion of harmful substances to the user 102.In some implementations, the air filter is located near the disposable pump 100 (as described below), so that air is expelled from the fluid substantially upstream and the fluid coming out of the air filter is primed (air-free) for infusion to user 102. Priming, in some implementations, means filling the medical tubing 106 with fluid so that it is ready to be infused into user 102. In some implementations, a second medical tube 112 is seamlessly coupled to the in-line air filter 108 (via an outlet in the in-line air filter 108). In some implementations, the first medical tube 106 and the second medical tube 112 are identical (e.g., same tube type (e.g., material), tube size (e.g., inner and outer diameter), tube length, etc.). In some other implementations, the first medical tube 106 and the second medical tube 112 are distinct (e.g., with one or more variations in tube type, tube size (e.g., inner and / or outer diameter), tube length, etc.). The first medical tube 106 and the second medical tube 112 are described in more detail below with reference to Figures 4A–4B. In addition or alternatively, in some implementations, an external flow restrictor 110 is attached to the first medical tube 106 (for example, via an external portion of the first medical tube 106) to provide and / or remove external pressure to the first medical tube 106. The external pressure to the first medical tube 106 is configured to close or open a fluid passage in the first medical tube 106 (for example, to stop or start fluid flow from the pump 100 by applying sufficient pressure to the first medical tube 106 to act as a shut-off valve). The external flow control 110 may be a slip clamp, a clamp-on clamp, a roller clamp, a screw clamp, and / or any other type of device capable of starting or stopping fluid flow from the disposable pump 100. Figure 2 illustrates an overview of the pump RfrCfr ίη / 77P7 / E / YILI disposable infusion pump 100 according to some implementations. In some implementations, the disposable pump 100 includes a housing 200, which is an assembly of a first part 202 and a second part 204. In some implementations, the first part 202 includes a first surface 402a (e.g., an outer or upper surface; shown in Figures 4A and 4B) and a second surface 402b directly opposite the first surface (e.g., an inner or lower surface (when the first part 202 and the second part 204 are coupled); shown in Figures 4A and 4B). In some implementations, the first surface of the first portion 202 includes an inlet 208 and an outlet 210 for receiving and distributing fluids, respectively. In some implementations, the second surface includes an elastic component 206 coupled between a first ring 410 and a second ring 414 (shown in Figures 4A and 4B).The first and second rings are attached to the second surface. In particular, in some implementations, the first ring is attached to the second surface via the edges 404 of the first part (e.g., as shown in Figures 4A and 4B). The elastic component 206, as described below, is configured to expand and store potential energy generated by the fluid within the infusion pump. As further shown in Figure 2, in some implementations, the first medical tube 106 is coupled to the outlet 210 (on the first surface) of the first part 202, so that the fluid can be dispensed from the disposable pump 100 (when filled with fluid as described below with reference to Figures 4A and 4B). Figure 3 is an overview of a pump system according to some implementations. In some implementations, the first part 202 (which includes a first surface 402a and a second surface 402b; shown in Figures 4A and 4B) of the housing 200 is made of a hard plastic, such as polycarbonate and / or other materials that are chemically compatible with the fluid to be infused into the user 102. In some implementations, the first part 202 has a parabolic shape (dome / diaphragm shape) with the second surface 402b extending in a direction opposite to the first surface 402a (e.g., the first surface is slightly serrated). In some implementations, the first part 202 is configured to stretch the elastic component 206 (through the second surface 402b) into a similar shape when assembled (e.g., as shown in Figures 4A and 4B).In some implementations, the second surface 402b of the first part 202 defines the shape of the elastic component 206 (for example, whether or not it stores potential energy). In some implementations, the edges 404 of the first part 202 are... RfrCfr ίη / ZZOZ / E / YILI extend outwards from the second surface 402b to provide a surface for coupling the elastic component 206 to the first part 202 (for example, via the upper rings 410 and lower rings 414 as described below). As will be appreciated by someone skilled in the art, the first part 202 of the housing 200 can be manufactured by injection molding, urethane casting, 3D molding, and / or other manufacturing processes. In some implementations, a valve sleeve 406 and a valve insert 408 are inserted into inlet 208 (for example, the valve sleeve 406 and valve insert 408 shown in Figures 4A and 4B). When inserted into inlet 208, the sleeve 406 and valve insert 408 create a one-way valve for the first part 202 of housing 200, allowing fluid flow in one direction (for example, externally through inlet 208). An important aspect of the disposable pump 100 is the ability to fill the disposable pump 100 with fluid through inlet 208 and to secure the fluid so that it cannot escape from the disposable pump 100 (for example, through inlet 208 and / or other parts of housing 200). In some implementations, a fluid is loaded into inlet 208 under pressure using a syringe (not shown) or other device to inject a fluid. In some implementations, the 100 disposable pump RfrCfr Ln / Zznz / E / YIAI includes at least two retaining rings (for example, an upper ring 410 and a lower ring 414). In some implementations, the upper ring 410 engages with a rib 412 that defines the elastic component 206 (for example, the rib 412 shown in Figures 4I and 4B). In some implementations, the upper ring 410 is also configured to engage with the lower ring 414 by effectively coupling the rib 412 of the elastic element 206 between the upper ring 410 and the lower ring 414. The upper ring 410 and the lower ring 414 can be made of any suitable rigid material, such as polycarbonate. The upper ring 410 and the lower ring 414, when joined together, support the elastic component 206 and provide a firm base for the elastic component 206 to expand and store potential energy, as described below with reference to Figures 4A and 4B. In some implementations, the elastic component 206 is substantially circular and flat when unexpanded (e.g., in a relaxed and / or unstretched state). As described above, the rib 412 defines the shape of the elastic component 206 (e.g., in a relaxed or pressurized state) and is configured to engage between the upper ring 410 and the lower ring 414. Traditionally, the elastic component 206 is composed of multiple layers of elastomeric material, with at least one layer being multi-layered. RfrCfr ίη / ZZOZ / E / YILI layers that act as a barrier against the drug. The multiple layers of elastic component 206 are used to contain the fluid drug. A drug barrier is a layer that protects the fluid (held by the multiple layers of elastic component 206) from contamination by other layers or by the multiple layers themselves. However, the drug barrier does not always prevent chemical leaching that occurs due to the material of the other layers of the multiple layers. Chemical leaching is the movement of contaminants and / or other water-soluble particles into the fluid drug. The elastomeric material includes natural rubber, isoprene, silicone, and / or other material that has high elastic memory (e.g., material that can expand and naturally or automatically returns to its relaxed state). To address the leaching problem, in some implementations, the elastic component 206 consists of a single layer. In some implementations, this single layer is injection-molded liquid silicone. In some implementations, the elastomeric material of the elastic component 206 has a uniform thickness. In some implementations, the elastomeric material of the elastic component 206 may have a thickness that varies along its length (provided the elastic component 206 can expand and store potential energy). RfrCfr ίη / ZZΖΠZΖ / E / YΙΛΙ variable can strengthen parts of the elastic component 206 that experience higher loads (e.g., higher loads on the edges of the elastic component 206, near the rib 412, when fluid is loaded into the disposable pump 100). In some implementations, the disposable pump 100 includes a second part 204 of the housing 200. The second part 204 may be a jar, bottle, and / or any other container with a shape having an opening to receive the first part 202 of the housing 200, which includes the elastic component 206. In some implementations, the second part 204 is made of a hard or semi-rigid plastic, such as PETG, which may be manufactured by processes such as blow molding and / or similar processes. In some other implementations, the second part 204 is made of glass. The elastic component 206 and the disposable pump 100 may be of various sizes, and the second part 204 may be sized accordingly. For example, the second part 204 may have an opening 416 large enough to accommodate the elastic component 206 and / or other components described herein, such as at least two retaining rings.Similarly, the second part 204 is configured to contain (e.g., enclose) the elastic component 206 when it is fully expanded. In some other implementations, the size of the second part... RfrCfr ίη / ZZΖΠZ / E / YΙΛΙ part 204 can be made compatible with the proposed maximum fluid capacity for the disposable pump 100 (as described below). In some implementations, the fluid (e.g., fluid medication) loaded into the disposable pump 100 via inlet 208 is configured to be delivered from outlet 210 through the first medical tube 106. The first medical tube 106 conveys the fluid from housing 200 at a first flow rate. The first flow rate is based, at least in part, on the potential energy stored by the elastic component 206 when it expands due to the fluid loaded at inlet 208 (e.g., via a syringe or similar device). In some implementations, the first flow rate is based on the inside diameter of the first medical tube 106, the length of the first medical tube 106, and / or other factors (e.g., fluid viscosity, temperature, pressure changes, etc.). In some implementations, the first flow rate is configured to quickly prime the infusion system for fluid delivery to the user 102.In some implementations, the first flow rate is selected based on the second flow rate (as explained below) to account for the increase in the total time required to prime the disposable pump 100. In other words, the first flow rate can be selected to quickly prime the disposable pump 100, while the second flow rate is set to... RfrCfr Ln / Zznz / E / YIAI deliver the fluid medication to the user 102 at the appropriate (e.g., selected) flow rate. In some implementations, the initial flow rate does not exceed 167 mL / h (±0.25 mL / h). In some implementations, the initial flow rate is between 5 mL / h and 167 mL / h. In some other implementations, more precise control of the initial flow rate can be achieved by reaching a flow rate of less than 5 mL / h (e.g., flow rates of approximately 2 mL / h ±0.25 mL / h). In some implementations, control of the initial flow rate can be achieved by adjusting the diameter and / or length of the initial medication tube 106. Different methods for controlling the flow rate are discussed below. In some implementations, an external flow restrictor 110 is attached to an outer portion of the first medical tube 106. The external flow restrictor 110 is configured to provide or remove external pressure to the first medical tube 106, thereby closing or opening a fluid passage within the first medical tube 106. In other words, in some implementations, the external flow restrictor 110 blocks the flow of liquid medication exiting the housing 200 (e.g., the fluid exiting through outlet 210). In some implementations, the external flow restrictor 110 blocks the fluid passage of the first medical tube 106, so that the fluid injected through inlet 208 expands the elastic component 206 (e.g., the disposable pump 100 can be filled without dispensing the fluids before sufficient potential energy is stored).In some implementations, the elastic component 206, when expanded, stores potential energy that is used to create a pressure differential for infusing the user 102. Therefore, the external flow restrictor 110 or a similar device is required to generate sufficient potential energy to ensure that the disposable pump 100 maintains a substantially constant fluid pumping pressure when the elastic component 206 contracts from an expanded to a relaxed state. It should be noted that the fluid injected into the disposable pump 100, through the inlet 208, must be charged with sufficient energy to overcome the resistance of the elastic component 206. In some implementations, a medical syringe and / or other fluid injection tool may be used to overcome the resistance of the elastic component 206. Further information regarding the elastic component 206 is described in Figures 4A and 4B below. In some implementations, an in-line air filter 108 is included in the infusion system. In some implementations, the air filter 108 is seamlessly coupled to a distal end of the first medical tubing 106 (for example, the end of the first medical tubing 106 opposite outlet 210) via an air filter inlet. Air filter 108 is located substantially upstream near outlet 210. In some implementations, air filter 108 is configured to expel air from the fluid through one or more air outlets. The air is expelled substantially upstream, so that the fluid exiting air filter 108 is primed without air. In some implementations, air filter 108 includes a membrane filter configured to remove one or more contaminants and particles from the fluid. In some implementations, the second medical tube 112 is seamlessly coupled to the air filter 108 via an outlet in the air filter. The second medical tube 112 is configured to adjust the first flow rate of the fluid delivered from housing 200, through the first medical tube 106, to a second flow rate. The second flow rate is based, at least in part, on the inside diameter of the second medical tube 112. In some other implementations, the second flow rate is based on the length of the first medical tube 106 and / or other factors (e.g., fluid viscosity, temperature, pressure changes, etc.). In some implementations, both the first and second flow rates are selected to quickly prime the disposable pump 100.For example, the first flow rate can be selected to be significantly higher than the second flow rate, so that the disposable device is substantially primed, leaving only a smaller portion of the disposable pump 100 to prime (e.g., the first flow rate). RfrCfr Ln / Zznz / E / YIAI can prime 3 / 4 of the disposable pump 100 (such as the length of the first medical tube 106 and the air filter 108), leaving only 1 / 4 to prime the second flow rate (such as the length of the second medical tube 112). In some implementations, the second flow rate does not exceed 5 mL / h. In some implementations, the second flow rate is between 2 mL / h and 5 mL / h. In some other implementations, the second flow rate is approximately 2 mL / h (e.g., approximately + / - 0.25 mL / h). In some implementations, more precise control of the second flow rate (e.g., less than 2 mL / h) can be achieved by adjusting the diameter and / or length of the second medical tube 112. In some implementations, the inside diameter of the second medical tube 112 is no greater than 0.0075 inches (0.1905 mm).In some implementations, the second medical tube 112 has a predetermined length that depends on the target flow rate (for example, a longer length results in a slower flow rate). In some modalities, the second medical tube 112 is used to adjust the flow rate of the fluid medication before dispensing it to the user 102. As mentioned earlier in Figure 1, the inside diameter of the first medical tube 106 and the inside diameter of the second medical tube 112 may be the same or different. Similarly, in some implementations, the length, material, and / or other parameters of the first medical tube 106 and the second medical tube 112 may be the same or different. The parameters for the first medical tube 106 and the second medical tube 112 depend on the flow rate required to infuse the fluid to the user 102. The second medical tube 112 is used to achieve the desired flow rate before the fluid is infused to the user 102. In some implementations, a 302 outlet of the second medical tube 112 (for example, a distal outlet) is fluidly coupled to the second medical tube 112. The 302 outlet of the second medical tube 112 is configured to connect to one or more components to deliver fluid to a user 102. In some implementations, the 302 outlet of the second medical tube 112 is a fixed male luer connector. In some implementations, one or more components configured to connect to the 302 outlet of the second medical tube 112 include a skin patch, needle, cannula, catheter, and / or other components for infusing the user 102. In some implementations, a flow restrictor component is placed inside the first medical tube 106 and / or the second medical tube 112. For example, the flow restrictor component may be located at a first location 304a inside the first medical tube 106 and / or a second location 304b inside the second medical tube 112. In some implementations, the flow restrictor may be placed at each location (for example, the first location 304a and the second location 304b). The flow restrictor component may be placed at any location inside the first medical tube 106 and / or the second medical tube 112. For example, the flow restrictor component may be placed next to outlet 210 of housing 200 (for example, inside the first medical tube 106), adjacent to an outlet 302 of the second medical tube 112, adjacent to the inlet or outlet of air filter 108, and / or at any point in between.In some implementations, the flow restrictor component is not fixed and is configured to move freely along the first medical tube 106 and / or the second medical tube 112. Alternatively or additionally, in some implementations, the flow restrictor component is fixed (anchored or clamped) in a particular location of the first medical tube 106 and / or the second medical tube 112 (e.g., such that the flow restrictor component does not move). The flow restrictor component is independent of the flow control provided by the first medical tube 106 and / or the second medical tube 112. In some implementations, the flow restrictor component includes one or more pins and / or beads, as described below in Figures 5A-6B. The flow restrictor component has a smaller diameter than the inside diameter of the first medical tube 106 and / or the second medical tube 112. In some implementations, the flow restrictor component has a larger diameter than the inlet and / or outlet of the air filter 108, such that the component The flow restrictor RfrCfr Ln / Zznz / E / YIAI remains within a particular location or portion of the tubing (for example, within the first medical tube 106 or the second medical tube 112). In some implementations, the flow restrictor component has a larger diameter than the outlet 302 of the second medical tube 112, so that the flow restrictor component does not flow toward user 102. Additionally, the flow restrictor component is configured not to break or separate as a user moves the first medical tube 106 and / or the second medical tube 112. The flow restrictor component is described in more detail in Figures 5A-6B. In some implementations, the disposable pump 100 includes a controller microcircuit (not shown) configured to operate a valve to control the first and / or second flow rates of the fluid. The controller microcircuit is described below in Figure 7. In some implementations, the controller microcircuit is a discrete component fluidly coupled in-line with one or more components of the disposable pump 100. For example, the controller microcircuit may be fluidly coupled between the outlet 210 of the disposable pump 100 and the first medical tube 106; the first medical tube 106 and the air filter 108; the air filter 108 and the second medical tube 112; and / or the second medical tube 112 and the outlet 302 of the second medical tube 112. Alternatively or additionally, in some implementations RfrCfr ίη / 77Π7 / E / YΙΛΙ The controller microcircuit is coupled to housing 200. The flow controller microcircuit is described in more detail with reference to Figure 7. Figures 4A and 4B illustrate cross-sectional views of the disposable pump 100, according to some implementations. More specifically, Figures 4A and 4B illustrate the expansion of the elastic component 206 as fluid is introduced through the inlet 208 of the housing 200 and into the fluid storage chamber 420 (which stores the potential energy generated by the expanded elastic component 206) under the pressure of a syringe or some other fluid-pumping tool. In some implementations, air is removed from the system (e.g., vented) through the outlet 210 along the notch 422, which is formed based on the second surface 402b. Figure 4A shows the upper ring 410 mated to the lower ring 414, with the rib 412 sandwiched between them. As mentioned earlier, the rib 412 defines the shape of the elastic component 206. In some implementations, the upper ring 410 and the lower ring 414 are mated by ultrasonic welding and / or solvent welding. In some implementations, the upper ring 410 is mated to the first part 202 (for example, through the edges 404), and the lower ring 414 is mated to the second part 204 using ultrasonic welding or solvent welding. RfrCfr Ln / Zznz / E / YIAI The elastic component 206 is inserted through the opening 416 of the second part 204 and creates the cavity 418 (for example, a space created within the housing 200). In some implementations, when the first part 202 and the second part 204 of the housing 200 are coupled together (via the upper ring 410 and lower ring 414), the second surface 402b of the first part 202 stretches the elastic component 206 into the shape of the second surface 402b (for example, as shown in Figures 4A and 4B). In some implementations, the dimensions of both the elastic component 206 and the second surface 402b are such that the elastic component 206 is stretched to a state where its elasticity is no longer linear.In particular, the elastic component 206 is stretched to a state where changes in the material stress of the elastic component 206 are not linearly proportional to changes in material stress during operation of the disposable pump 100. Figures 4B show a cross-sectional view of the disposable pump 100 after fluid has been injected through the inlet 208 of the first part 202 of the housing 200, according to some implementations. In some implementations, the injected fluid expands the elastic component 206 to create an expanded fluid storage 420. The expanded fluid storage 420 is under pressure from a syringe and / or other tool used RfrCfr ίη / ZZOZ / E / YILI to inject fluid (through inlet 208) into the disposable pump 100 (after the air has been removed from the system through the outlet (through inlet 210) along the notch 422, which is formed based on the second surface 402b. As mentioned above, an external flow restrictor 110 can be used to block a fluid passage of the first medical tubing 106, so that fluid does not exit outlet 210, allowing the fluid storage 420 to expand as fluid is injected into the disposable pump 100. To create a substantially constant fluid pumping pressure in the fluid storage 420, the expansion and subsequent contraction of the elastic component 206 is achieved when, before fluid is injected into inlet 208, the elastic component 206 stretches to a state where its elasticity is not linear.As mentioned previously, this state is achieved by the shape and / or dimensions of the second surface 402b and / or the elastic component 206 during the assembly of the housing 200. It should be noted that the medical syringe (not shown) and / or any other tool used to inject the fluid into the disposable pump 100 must inject the fluid with sufficient force to overcome the current state of the elastic component 206 (e.g., sufficient force to overcome the force generated by the elastic component 206 to contract). The elastic component 206 must stretch non-linearly to form [forms]. RfrCfr Ln / Zznz / E / YIAI expand fluid storage 420 as shown in Figure 4B. In some implementations, the 420 fluid storage system is configured to expand to hold a volume of at least 50 mL of fluid. In some other implementations, the 420 fluid storage system is configured to expand to hold a volume of at least 100 mL of fluid. In still other implementations, the 420 fluid storage system is configured to expand to hold a volume of at least 250 mL of fluid. In general, a fluid must be introduced under sufficient pressure to overcome the potential energy of the initially stretched elastic component 206 (stretched by the second surface 402b). Similarly, a fluid must be introduced under sufficient pressure to further (non-linearly) stretch the elastic component 206 and form the fluid storage 420. The potential energy stored by the fluid storage 420 is the total amount of energy available for discharging the fluid (e.g., out of outlet 210). The fluid storage 420, even after complete discharge, retains residual potential energy because the elastic component 206 is stretched over the second surface 402b. The fluid flow through the first medical tube 106 and / or the second medical tube 112 can be characterized by the RfrCfr Ln / Zznz / E / YIAI Hagen-Poiseuille equation. The flow can be characterized by the Hagen-Poiseuille equation because the flow through the first medical tube 106 and / or the second medical tube 112 is assumed to be laminar. Furthermore, due to the characteristics of the elastic component 206 (e.g., elastomeric material that applies constant pressure to the stored fluids), the pressure generated by the disposable pump 100 (device P) is considered constant. At the same time, the pressure generated by the patient (P_patient) is also assumed to be effectively constant. With these assumptions, the following Hagen-Poiseuille equation can be used to define the fluid flow from the disposable pump 100 to the user 102: P_device-P_patient = flow rate * (resistance of the restrictor) This equation can also be characterized as y = ——, 128μ£' where: V = fluid flow velocity; D = the diameter of the flow restrictor duct; Δρ = energy loss (i.e., pressure change over a length L); L = length of the flow restrictor; and μ = viscosity of the fluid. According to the Hagen-Poiseuille equation, if there is If there is a constant energy loss along a tube (as assumed in the present implementations), then a constant fluid flow rate through a tube can be achieved (e.g., by designing the first medical tube 106 and / or the second medical tube 112 as described herein). A constant energy loss along a tube (e.g., the first medical tube 106 and / or the second medical tube 112) can be assumed because, as mentioned above, P_device and P_patient are considered constant. In practice, P_patient is negligibly small. As such, the flow from the disposable pump 100 is almost entirely due to the constant pressure produced by the stored potential energy of the elastic element 206. In other words, to determine a specific value for the fluid flow rate of the disposable pump 100 through the first medical tube 106 and / or the second medical tube 112 to the user 102, the device's P and the physical design of the first medical tube 106 and / or the second medical tube 112 must be considered together. In particular, the pressure sustained by the elastic component 206 (e.g., stored potential energy) is used in conjunction with the respective diameter and / or length of the first medical tube 106 and / or the second medical tube 112 to determine the flow rate of the disposable pump 100. RfrCfr ίη / ΖΖΠΖ / Ε / ΥΙΛΙ Figures 5A and 5B illustrate a flow restrictor component according to some implementations. Figure 5A shows a tube segment 502 (e.g., the first medical tube 106 and / or the second medical tube 112) that includes a flow-restricting component, such as a pin 506. In some implementations, the pin 506 has a smaller diameter than the inside diameter of the tube segment 502, so that the pin 506 can be located inside the tube segment 502. In some implementations, the pin 506 has a larger diameter than the inlet and / or outlet of the air filter 108 and / or the outlet 302 of the second medical tube 112. In this way, the pin 506 remains inside the tube segment 502 without moving between different tube segments (e.g., from the first medical tube 106 to the second medical tube 112 and vice versa) and / or to prevent the pin 506 from being infused into the user 102.In some implementations, pin 506 is either fixed (anchored in a particular location) or non-fixed (movable along its length) within segment tube 502. In some implementations, pin 506 has a predetermined length. In some implementations, pin 506 is made of glass or metal. In some implementations, pin 506 is configured to adjust (e.g., decrease) the flow rate (e.g., the first or second flow rate as described earlier in Figure 3). In some implementations, the flow rate adjustment is based, in part, on the pin diameter. 506. In some implementations, pin 506 is configured to change the fluid shape from a cylindrical shape (e.g., cylindrical flow 504) to a torus shape (e.g., donut or toroidal flow 508). For example, as shown in Figure 5A, pin 506 changes the cylindrical flow 504 to a toroidal flow 508, where the radius of the toroidal flow 508 is based, in part, on the diameter of pin 506. Although the toroidal flow 508 is shown as a single ring, it should be noted that the toroidal flow 508 is a continuous stream (as shown in Figure 5B). In some implementations, the change in flow shape decreases the flow rate by interrupting the flow and causing it to move around pin 506 (e.g., without causing the tube segment 502 to expand or change shape). In some implementations, the flow rate is also based, in part, on the predetermined length of pin 506. Figure 5B shows a partial cross-sectional side view of the flow restrictor component in Figure 5A. As shown in Figure 5B, the cylindrical flow 504 flows from the disposable pump 100 (for example, through outlet 210) to the distal end (end opposite outlet 210 of the disposable pump 100) of the tube segment 502. In some implementations, the pin 506 reduces the flow rate of the cylindrical flow 504 by reducing the cross-sectional area of ​​the cylindrical flow 504 by the area of ​​the section RfrCfr Ln / Zznz / E / YIAI cross-section of pin 506 and thus changing the flow to a toroidal flow 508. In particular, the cylindrical area of ​​the tube segment 502 is reduced by the cross-sectional area of ​​pin 506. In some implementations, pin 506 creates an annular section (e.g., the length of pin 506) within the tube segment 502. The flow within the annular section of the tube segment 502 follows the following Poiseuille equation: Q = = R1 where: Q = flow rate; Ri = the radius of pin 506; R2 = the radius of tube segment 502; G = the change in pressure over the length; and μ = viscosity of the fluid. As mentioned previously, the pressure change can be assumed to be constant along a tube (e.g., the first medical tube 106 and / or the second medical tube 112) because P_device and P_patient are considered to be constant. Using the equation above, a constant fluid flow rate can be achieved through a tube segment 502 with pin 506 (e.g., by designing the first medical tube 106, the second medical tube 112, and / or pin 506 as described herein). In other words, for To determine a specific flow rate for the fluid in the disposable pump 100 through the first medical tube 106 and / or the second medical tube 112 with a pin 506, the device pressure (P_device) and the physical design of the first medical tube 106, the second medical tube 112, and / or the pin 506 must be considered together. In particular, the pressure maintained by the elastic component 206 (e.g., the stored potential energy) is used in conjunction with the respective diameters of the first medical tube 106, the second medical tube 112, and / or the pin 506 to determine the flow rate for the disposable pump 100. In practice, patient pressure (P_patient) is negligibly small. As such, the flow rate of the disposable pump 100 is almost entirely due to the constant pressure produced by the stored potential energy of the elastic element 206. Figures 6A and 6B illustrate another flow-restricting component according to some implementations. In Figure 6A, a tube segment 502 (e.g., the first medical tube 106 and / or the second medical tube 112) is shown, which includes another flow-restricting component, such as one or more rigid beads 602. In some implementations, one or more rigid beads 602 have a smaller diameter than the inside diameter of the tube segment 502, so that one or more rigid flanges 602 can be located within the tube segment 502. In some implementations, one or more rigid 602 beads have a larger diameter than the inlet and / or outlet of the RfrCfr ίη / ZZΖΠZ / E / YΙΛΙ air filter 108 and / or the outlet 302 of the second medical tube 112. In this way, one or more rigid beads 602 remain within the tube segment 502 without moving between different tube segments (for example, from the first medical tube 106 to the second medical tube 112 and vice versa) and / or to prevent one or more rigid beads 602 from being infused to the user 102. In some implementations, one or more rigid beads 602 are fixed (anchored) or non-fixed (movable) within the tube segment 502. In some implementations, each rigid bead of one or more rigid beads 602 is the same. In some other implementations, at least one rigid bead (or all) of one or more 602 rigid beads may have a different transport size (e.g., one or more 602 rigid beads have variable diameters). In some implementations, the 602 rigid beads may be made of glass or metal. Depending on various factors, the rigid beads can be sized so that their placement does not cause the pipe (e.g., the 502 pipe segment) to expand. As mentioned earlier, in some implementations, one or more 602 rigid beads have a smaller diameter than the inside diameter of the 502 pipe segment. In this respect, the flow rate through the pipe segment can be defined, at least in part, as a function of the cross-sectional area or diameter of the bead(s) within the pipe, the difference between RfrCfr Ln / Zznz / E / YIAI the cross-sectional area or bead diameter and the internal diameter of the pipe, and / or the number of beads within the pipe or their collective mass within a predetermined area of ​​the pipe segment 502. In some implementations, one or more rigid beads 602 are configured to adjust (e.g., decrease) the flow rate (e.g., the first or second flow rate as described earlier in Figure 3). In some implementations, the flow rate adjustment is based, in part, on the diameter of one or more rigid beads 602. In particular, one or more rigid beads 602 are configured so that the fluid (e.g., cylindrical flow 504) moves around their surface or diameter (e.g., without causing the tube segment 502 to expand or change shape). The flow rate is based, in part, on the diameter of one or more rigid beads (e.g., the area around which the fluid must move). In some implementations, the flow rate is further based on the number of one or more rigid beads 602 within the tube segment 502 (e.g., each additional rigid bead 602 decreases the flow rate). Figure 6B shows a partial cross-sectional side view of the flow-restricting component of Figure 6A. As shown in Figure 6B, at least two rigid beads of one or more rigid beads 602 are inside the pipe segment 502. Figure 6B also shows the RbCb ίη / 77Π7 / E / YΙΛΙ cylindrical flow 504 flowing from the disposable pump 100 (e.g., through outlet 210) into the distal end (end opposite outlet 210 of the disposable pump 100) of the tube segment 502. In some implementations, one or more rigid beads 602 reduce the flow rate of the cylindrical flow 504 by reducing the cross-sectional area of ​​the cylindrical flow 504 by the cross-sectional area of ​​one or more rigid beads 602. In particular, the cylindrical area of ​​the tube segment 502 is reduced by the cross-sectional area of ​​one or more rigid beads 602. In some implementations, the flow within the tube segment 502 with one or more rigid beads 602 follows the Poiseuille equations described above (e.g., derived from the respective diameters and / or circumference of one or more rigid beads 602). As mentioned earlier in Figures 5A and 5B, the pressure change can be assumed to be constant along a tube (e.g., the first medical tube 106 and / or the second medical tube 112) because P_device and P_patient are considered constant. Using Poiseuille's equations, a constant fluid flow rate can be achieved through a tube segment 502 with one or more rigid beads 602 (e.g., by designing the first medical tube 106, the second medical tube 112, and / or one or more rigid beads 602 as described herein). In other words, to determine a flow rate RfrCfr ίη / ZZOZ / E / YILI specific for the fluid of the disposable pump 100 through the first medical tube 106 and / or the second medical tube 112 with one or more rigid beads 602, the P_device and the physical design of the first medical tube 106, the second medical tube 112 and / or one or more rigid beads 602 must be considered together. In particular, the pressure maintained by the elastic component 206 (e.g., the stored potential energy) is used together with the respective diameter of the first medical tube 106, the second medical tube 112 and / or one or more rigid beads 602 to determine the flow rate for the disposable pump 100. In practice, P_patient is negligibly small. As such, the flow of the disposable pump 100 is due almost entirely to the constant pressure produced by the stored potential energy of the elastic element 206. In some implementations, the different flow restriction components can be combined in the 502 pipe segment. For example, in some implementations, the 502 pipe segment may include the 506 pin and one or more 602 rigid beads. Figure 7 is a block diagram representing a flow controller 700 according to some implementations. In some implementations, the disposable pump 100 includes a flow controller 700 that is configured to control the flow of fluid discharged from the disposable pump 100. In some implementations, the The flow controller 700 is coupled to the housing (e.g., through the first 202 and / or second part 202 of the housing 200). Alternatively, in some implementations, the flow controller 700 is seamlessly coupled in-line with the first medical tube 106, the second medical tube 112, and / or other components of the disposable pump 100 (e.g., between the first medical tube 106 and outlet 210, the first medical tube 106 and air filter 108, etc.). In some implementations, the flow controller 700 operates one or more cushions (e.g., expandable components for blocking a fluid passage), a valve, and / or similar components to control the available fluid passage from the disposable pump 100 and select a desired flow rate. In some implementations, one or more pillows, valve and / or similar components are placed adjacent to (e.g., before or after) the outlet 210 of the disposable pump 100.In some implementations, the flow controller 700 (which includes one or more pads, the valve, and / or similar components) is a discrete component fluidly coupled in-line with one or more components of the disposable pump 100 (for example, so that fluid enters an inlet of the flow controller 700 at a first flow rate and exits through an outlet of the flow controller 700 at a second user-selected flow rate 102). Additionally or alternatively, in some implementations, one or more pads, the valve. RfrCfr Ln / Zznz / E / YIAI and / or similar components are placed with the first medical tube 106 and / or the second medical tube 112. The flow controller 700 is set to achieve a selected flow rate as low as 0.48 mL / h. The flow controller 700 includes one or more processing units (including, for example, a processor, processor core, or other type of controller microcircuit) 702, one or more networks or other communication interfaces 704 (for example, one or more antennas), memory 712, one or more sensors 708, and one or more communication data transfer pathways 710 to interconnect these components. The communication data transfer pathways 710 optionally include circuitry (sometimes referred to as a chipset) that interconnects and controls communication between the system components. In some implementations, the flow controller 700 may include external interfaces 706 for manual control of the flow controller 700.In some implementations, one or more external interfaces 706 of the flow controller 700 may include, for example, input devices such as a keyboard, mouse, touch-sensitive surfaces and / or controllers, a tracking pad, USB devices, and / or input buttons. In some implementations, sensors 708 are used to collect data on flow rate and the pressure maintained within the elastic component 206 (e.g., storage). RfrCfr Ln / Zznz / E / YIAI of fluids 420) and / or other information necessary to determine the flow rate of the disposable pump 100. One or more components of the flow controller 700 are sterilized to prevent contamination of the fluid drug. Similarly, one or more components of the flow controller 700 are separated from the flow line of the disposable pump 100 (with the exception of one or more pads, the valve, and / or similar components) to further prevent contamination and / or to prevent the fluid from damaging the flow controller 700. Memory 712 can be high-speed random-access memory, such as DRAM, SRAM, DDR RAM, or other random-access solid-state memory devices, and can include non-volatile memory, such as one or more disk storage devices, optical disc storage devices, flash memory devices, and / or other non-volatile solid-state storage devices. In some implementations, memory 712 includes one or more storage devices located remotely from the 702 processor(s). Memory 712, or alternatively, the non-volatile memory device(s) within memory 712, includes a non-transient, computer-readable storage medium. In some implementations, memory 712 or the computer-readable storage medium of memory 712 stores programs, modules, and / or data structures that can be used to RfrCfr Ln / Zznz / E / YIAI perform one or more flow controller operations 700. For example, memory 712 may include programs, modules and / or data structures for an operating system 714, a network communication module 716, a flow control module 718 and a device information database 720. In some implementations, the operating system module 714 may include procedures for handling various basic system services and for performing hardware-dependent tasks. The network communication module 716 may be configured to connect the flow controller 700 to other computing devices through one or more communication network interfaces 704 (wired or wireless) and one or more communication networks, such as Ethernet, Wi-Fi, Bluetooth, an Integrated Services Digital Network (ISDN) connection, a Digital Subscriber Line (DSL) modem, or a cable modem.Any direct or indirect network connection can be used, including but not limited to a telephone modem, MIB system, RS232 interface, auxiliary interface, optical link, infrared link, radio frequency link, microwave link, WLAN connection, or other wireless connection. The 718 flow control module is configured to adjust the flow rate as desired. In some implementations, the flow control module 718 determines the flow rate using the Hagen-Poiseuille equations described above. In particular, the flow control module 718 can determine the flow rate using data collected from one or more sensors 708 and the device information database 720. In some implementations, the flow control module 718 is configured to operate automatically (e.g., tamper-proof software (firmware) designed to achieve and / or maintain a desired flow rate). Alternatively or additionally, in some implementations, the flow controller 700 and the flow control module 718 can be manually operated by a user 102 via external interfaces 706 and / or communication interfaces 704 (e.g., receiving wireless controls from a remote device, such as a laptop, computer, mobile phone, tablet, etc.).In some implementations, the disposable pump 100 can be controlled via a dedicated application. The device information database 720 includes data for the disposable pump 100, such as the length of the first medical tube 106 and / or the second medical tube 112, the diameter of the first medical tube 106 and / or the second medical tube 112, the maximum capacity of the elastic component 206, and the pressure (e.g., potential energy) stored by the elastic component 206 while under different loads. RfrCfr Ln / Zznz / E / YIAI fluid quantities, the viscosity of one or more different types of fluids and / or other useful information. Figures 8A-8D are flow diagrams illustrating a method 800 for controlling the flow rate of the disposable pump 100 according to some implementations. The method 800 can be carried out on a disposable pump 100, the disposable pump 100 comprising at least a housing 200 including an elastic component 206. The disposable pump 100 further comprises at least a first fluid tube (e.g., the first medical tube 106) coupled to the housing 200 through an outlet 210; an air filter 108 fluid-coupled to a distal end of the first tube (e.g., the first medical tube 106) through an air filter inlet; a second tube (e.g., the second medical tube 112) fluid-coupled to the air filter 108 through an air filter outlet; and an outlet 302 of the second medical tube 112 fluid-coupled to the second tube.In some implementations, the housing 200 includes a first part 202 comprising a first surface 402a and a second surface 402b. The first surface 402a includes the outlet 210 for distributing the fluid, and the second surface 402b is opposite the first surface 402a. In some implementations, the elastic component 206 is coupled between a first ring 410 and a second ring 414. The first ring 410 and the second ring 414 are fixed to the second surface 402b. RfrCfr Ln / Zznz / E / YIAI implementations, the disposable pump 100 further comprises at least a second part 204 configured to accommodate the second surface 402b of the first part 202, the first part 202 and the second part 204 being coupled. Methods consistent with this description may include at least some, but not all, of the operations illustrated in Method 800, performed in a different sequence. Furthermore, methods consistent with this description may include at least two or more steps as in Method 800 performed overlapping in time, or nearly simultaneously. Method 800 includes expanding (802) the elastic component 206 with the fluid to store potential energy generated by the fluid within the infusion pump 100. In some implementations, the elastic component includes (804) an elastomeric membrane. In some implementations, the membrane is (806) a single layer of silicon. In some implementations, the elastic component 206 is configured to expand (808) and contain a volume of at least 50 mL. In some implementations, the elastic component 206 is configured to expand (810) and contain a volume of at least 100 mL. In some implementations, the elastic component 206 configured to expand (812) contains a volume of at least 250 mL. In some implementations, the elastic component is RfrCfr ίη / ZZOZ / E / YILI form by a single-layer membrane and the housing 200 (of the infusion pump) includes an inlet 208 for receiving the fluid, and the method 800 includes receiving (814) the fluid through the inlet; and expanding the elastic component 206 and generating the potential energy stored by the elastic component 206 based on the fluid received through the inlet. Method 800 involves directing (816), from the first tube (for example, the first medical tube 106), the fluid from the housing 200 at a first flow rate based, in part, on the potential energy stored by the elastic component 206. In some implementations, the first flow rate is further based (818), at least in part, on an inside diameter of the first tube. In some implementations, the first flow rate is further based (820), at least in part, on a length of the first tube. The flow rate determinations are based on the potential energy stored by the elastic component 206 and the Hagen-Poiseuille equations, as described earlier in Figures 4A-6B. In some implementations, the infusion pump further includes (822-a) an external flow restrictor 110 attached to an outer portion of the first tube, and Method 800 includes, in the infusion pump, providing (822-b), through the external flow restrictor 110, external pressure to the first tube that closes off a fluid passage in the first tube. In some implementations, Method 800 includes removing (822-c), a RfrCfr Ln / Zznz / E / YIAI through the external flow restrictor 110, the external pressure of the first tube opening the fluid passage of the first tube. As described above in Figures 4A and 4B, the external flow restrictor 110 can be used to load (e.g., inject fluid) the elastic component 206 (e.g., expand the elastic component 206 to create the fluid storage 420). Method 800 includes expelling (824) air from the fluid through one or more vent holes in air filter 108. The air is expelled substantially upstream, so that the fluid leaving the air filter is primed without air. In some implementations, the air filter includes (826) a membrane filter, and Method 800 includes, at the infusion pump, the removal of one or more contaminants and particles from the fluid. Method 800 includes adjusting (828) the first flow rate of the fluid conveyed from housing 200, through the first tube, to a second flow rate, the second flow rate being based, at least in part, on an inside diameter of the second tube (for example, the second medical tube 112). In some implementations, the inside diameter of the second tube (830) is no greater than 0.0075 inches (0.1905 mm). In some implementations, the second tube (832) has a predetermined length, and the second flow rate is further based on the predetermined length. In some implementations, the The inner diameter of the first tube and the inner diameter of the second tube are (834) equal. In some implementations, the inner diameter of the first tube and the inner diameter of the second tube are (836) different. In some implementations, the second flow rate is (838) no greater than 5 mL / h. In some other implementations, the second flow rate is (840) approximately 2 mL / h (approximately, in some implementations, means + / - 0.2 mL / h). The flow rate determinations are based on the potential energy stored by the elastic component 206 and the Hagen-Poiseuille equations, as described earlier in Figures 4A-6B. Method 800 includes distributing (842) the fluid to a user 102 through one or more components fluidly coupled to the outlet 302 of the second medical tube 112. In some implementations, the outlet 302 of the second medical tube 112 is (844) a fixed male luer fitting. In some implementations, one or more components configured to connect to the outlet 302 of the second medical tube 112 include (846) a skin patch, a needle, a cannula, and a catheter. In some implementations, the infusion pump includes (848) a flow-restricting component (e.g., pin 506 and / or rigid beads 602) within the first tube; the flow-restricting component has a smaller diameter than the inside diameter of the first tube. In some implementations, RfrCfr Ln / Zznz / E / YIAI The diameter of the flow restrictor component (850) is larger than the diameter of the air filter inlet and / or outlet 108 and / or the outlet 302 of the second medical tube 112. In this way, the flow from the restrictor component remains within a particular tube segment and / or is not infused into the user 102 (as described above in Figures 5A-6B). In some implementations, the flow restrictor component (852) is not fixed within the first tube. In some other implementations, the flow restrictor component (854) is fixed within the first tube. Although the example provided herein has the flow restrictor component in the first tube, it should be noted that the flow restrictor component could be in the second tube and / or in both the first and second tubes. In some implementations, the flow-restricting component is (856) a pin 506 configured to change the fluid shape from a cylindrical shape (e.g., cylindrical flow 504) to a torus shape (e.g., toroidal flow 508). In some implementations, the pin 506 has (858) a predetermined radius, and the initial flow rate is also based, in part, on the radius of the pin 506. In some implementations, the pin 506 has (860) a predetermined length, and the initial flow rate is also based, in part, on the predetermined length of the pin. The effects of the pin 506 on the flow are discussed above with RfrCfr Ln / Zznz / E / YIAI reference to Figures 5A and 5B. In some implementations, pin 506 (862) is made of glass or metal. In some other implementations, the flow-restricting component (864) is one or more rigid beads configured so that the fluid moves around the diameter of one or more rigid beads. The first flow rate is also based, in part, on the diameter of one or more rigid beads, and one or more rigid beads do not cause the first tube to expand as the fluid moves around the diameter of one or more rigid beads. In some implementations, one or more rigid beads may be (866) of variable size. In particular, all the rigid beads may be identical (having the same diameters) or dissimilar (having different diameters among the rigid beads). The effects of one or more rigid beads 602 on the flow were described earlier with reference to Figures 6A and 6B. In some implementations, at least two rigid beads (868) are included in the first tube.In some implementations, one or more rigid beads are (870) made of glass or metal. In some implementations, the infusion pump also includes a controller microcircuit (for example, the flow controller 700), and method 800, in the infusion pump, operates (872) a valve to control the initial fluid flow rate. In some implementations, the controller microcircuit is controlled (874) via a RfrCfr Ln / Zznz / E / YIAI USB. In some other implementations, the controller microcircuit (876) is controlled wirelessly (for example, via wireless protocols such as Bluetooth or a dedicated application). In some implementations, the controller microcircuit includes tamper-proof software (firmware) (878) to automatically control the flow rate. The flow controller 700 is controlled to achieve a selected flow rate (for example, as low as 0.48 mL / h). In some implementations, one or more components of the flow controller 700 (for example, the wireless component 704, the external interfaces 706, the sensors 708, etc.) are sterilized and separated from the fluid path so that the fluid drug is not contaminated. The flow controller 700 was described in detail above with reference to Figure 7. The foregoing description is provided to enable a person experienced in the technique to practice the various configurations described herein. While the technology in question has been described specifically with reference to the various figures and configurations, it should be understood that these are for illustrative purposes only and should not be considered as limiting the scope of the technology in question. Those experienced in the technique will appreciate that the various illustrative blocks, modules, elements, components, methods, and algorithms described herein can RfrCfr ίη / ZZΖΠZ / E / YΙΛΙ can be implemented as electronic physical elements (hardware), computer programming elements (software), or combinations of both. To illustrate this interchangeability of physical and programming elements, several illustrative blocks, modules, elements, components, methods, and algorithms have been described above in general terms of their functionality. Whether such functionality is implemented as physical or programming elements depends on the particular application and the design constraints imposed on the overall system. The described functionality can be implemented in various ways for each particular application. Various components and blocks can be arranged differently (e.g., in a different order or divided differently) without deviating from the scope of the technology in question. The specific order or hierarchy of steps in the described processes is understood to be an illustrative example of approaches. Based on design preferences, the specific order or hierarchy of steps in the processes may be rearranged. Some steps may be performed concurrently. The claims of the attached method present elements of the various steps in a sample order and are not intended to be limited to the specific order or hierarchy presented. Illustration of the technology in question as clauses: RfrCfr Ln / Zznz / E / YIAI Several examples of aspects of the description are described as numbered clauses (1, 2, 3, etc.) for convenience. These are provided as examples and do not limit the technology in question. The figure identifications and reference numbers provided below are simply examples and for illustrative purposes, and the clauses are not limited by such identifications. Clause 1. An infusion pump comprising: a housing including an elastic component configured to expand and store potential energy generated by the fluid within the infusion pump, and a first tube fluidly coupled to an outlet of the housing, the first tube configured to conduct the fluid from the housing at a first flow rate based, in part, on the potential energy stored by the elastic component; an air filter fluidly coupled to a distal end of the first tube through an air filter inlet, the air filter configured to expel air from the fluid through one or more air outlets, wherein the air is expelled substantially upstream, so that the fluid exiting the air filter is primed without air;a second tube fluid-coupled to the air filter via an outlet of the air filter, wherein: the second tube is configured to adjust the first flow rate of the fluid conducted from the housing, through the first tube, to a second flow rate, the second flow rate being based, therefore; RbCb ίη / 77Π7 / E / YΙΛΙ less in part, in an inner diameter of the second tube, and an outlet of the second tube is configured to smoothly couple to one or more components to distribute the fluid to a user. Clause 2. The infusion pump of Clause 1, wherein the inside diameter of the second tube is not greater than 0.0075 inches (0.1905 mm). Clause 3. The infusion pump of any of the above Clauses, the second tube has a predetermined length, and the second flow rate is further based on the predetermined length. Clause 4. The infusion pump of any of the preceding Clauses, wherein the inside diameter of the first tube and the inside diameter of the second tube are equal. Clause 5. The infusion pump of any of the Clauses 1 to 3, where the inside diameter of the first tube and the inside diameter of the second tube are different. Clause 6. The infusion pump of any of the Previous clauses, which further comprise a flow restricting component within the first tube, wherein the flow restricting component has a smaller diameter than the inside diameter of the first tube. Clause 7. The infusion pump of Clause 6, wherein the flow-restricting component is a pin configured to change the shape of the fluid in a way RfrCfr ίη / 77Ω7 / Β / YILI cylindrical to a toroidal shape, wherein: the pin has a predetermined radius, and the first flow rate is also based, in part, on the predetermined radius of the pin. Clause 8. The infusion pump of any of Clauses 6 and 7, wherein the flow-restricting component is a pin configured to change the shape of the fluid from a cylindrical shape to a toroidal shape, wherein: the pin has a predetermined length, and the first flow rate is further based, in part, on the predetermined length of the pin. Clause 9. The infusion pump of any of Clauses 6 to 8, wherein the flow-restricting component is one or more rigid beads configured so that the fluid moves around a diameter of one or more rigid beads, wherein: the first flow rate is further based, in part, on the diameter of one or more rigid beads, and one or more rigid beads do not cause the first tube to expand while the fluid moves around the diameter of one or more rigid beads. Clause 10. The infusion pump of Clause 9, wherein at least two rigid beads are included in the first tube. Clause 11. The infusion pump of any of Clauses 6 to 10, wherein the flow restrictor component is not fixed within the first tube and is configured to move a length of the first tube. RfrCfr Ln / Zznz / E / YIAI Clause 12. The infusion pump of any of Clauses 6 to 10, wherein the flow restrictor component is fixed inside the first tube and configured to remain in a predetermined location of the first tube. Clause 13. The infusion pump of any of the preceding Clauses, wherein the outlet of the second tube is a fixed male luer. Clause 14. The infusion pump of any of the preceding Clauses, wherein the air filter includes a membrane filter configured to remove one or more contaminants and particles from the fluid. Clause 15. The infusion pump of any of the preceding Clauses, further comprising an external flow restrictor coupled to an outer portion of the first tube, the external flow restrictor being configured to provide or remove external pressure to the first tube that respectively closes or opens a fluid passage of the first tube. Clause 16. The infusion pump of any of the preceding Clauses, further comprising a controller microcircuit configured to operate a valve to control the first flow of the fluid. Clause 17. The infusion pump of any of the above Clauses, wherein the second flow rate does not exceed 5 mL / h. Clause 18. The infusion pump of any of the RfrCfr ίη / ΖΖΩΖ / Ε / ΥΙΛΙ Previous clauses, where one or more components configured to connect to the outlet of the second tube include a skin patch, a needle, and a catheter. Clause 19. The infusion pump of any of the preceding Clauses, wherein: the elastic component is formed by a single-layer membrane; and the housing includes an inlet for receiving the fluid, the fluid received through the inlet expands the elastic component and generates the potential energy stored by the elastic component. Clause 20. The infusion pump of Clause 19, wherein the single-layer membrane is an elastomeric membrane. Clause 21. The infusion pump of any of the preceding Clauses, wherein the elastic component is configured to expand to contain a volume of at least 50 mL of the fluid. Clause 22. The infusion pump of any of the preceding Clauses, wherein: the housing includes: a first part comprising a first and a second surface, wherein: the first surface includes the outlet of the housing for fluid distribution, and the second surface, opposite the first surface, includes the elastic component coupled between a first ring and a second ring fixed to the second surface; a second part configured to house the second surface of RfrCfr Ln / Zznz / E / YIAI the first part, where the first part and the second part are coupled.Clause 23. A method for infusing fluid into a patient, the method comprising: an infusion pump comprising: a housing including an elastic component; a first tube fluid-coupled to the housing via an outlet of the housing, an air filter fluid-coupled to a distal end of the first tube via an air filter inlet, a second tube fluid-coupled to the air filter via an air filter outlet, and an outlet of the second tube fluid-coupled to one or more components; expanding the elastic component with the fluid to store potential energy generated by the fluid within the infusion pump; conducting, from the first tube, the fluid from the housing at a first flow rate based, in part, on the potential energy stored by the elastic component;expelling air from the fluid through one or more air filter vent holes, where the air is expelled substantially upstream, so that the fluid leaving the air filter is primed without air; adjusting the first flow rate of the fluid conveyed from the housing, through the first tube, to a second flow rate, the second flow rate being based, at least in part, on an inside diameter of the second tube; and distributing the fluid to a user through one or more components. Additional consideration: The specific order or hierarchy of steps in the described processes is understood to be an illustrative example of approaches. Based on design preferences, the specific order or hierarchy of steps in the processes may be rearranged. Some steps may be performed concurrently. The claims of the attached method present elements of the various steps in a sample order and are not intended to be limited to the specific order or hierarchy presented. There may be many other ways to implement the technology in question. Several functions and elements described herein can be divided differently than shown without departing from the scope of the technology in question. Several modifications to these configurations will be readily apparent to those skilled in the art, and the generic principles defined herein can be applied to other configurations. Therefore, many changes and modifications can be made to the technology in question by someone skilled in the art without departing from its scope. As used herein, the phrase "at least one of" preceding a series of items, with the term "yuo" separating any of the items, modifies the list as a whole, rather than each item in the list (for (RfrCfr Ln / Zznz / E / YIAI example, each point). The phrase "at least one of" does not require the selection of at least one of each listed item; rather, the phrase allows for a meaning that includes at least one of any of the items, and / or at least one of any combination of the items, and / or at least one of each item. For example, the phrases "at least one of A, B, and C" or "at least one of A, B, or C" each refer to only A, only B, or only C; any combination of A, B, and C; and / or at least one of each of A, B, and C. Furthermore, to the extent that the term "include," "have," or similar is used in the description or claims, such term is intended to be inclusive in a manner similar to the term "comprise," which is understood to be inclusive when used as a transitional word in a claim. The word "exemplary" is used herein to mean "serves as an example," "instance," or "illustration." Any embodiment described herein as exemplary should not necessarily be construed as preferred or advantageous over other implementations. A reference to a singular element is not intended to mean one and only one, unless specifically stated, but one or more. The term "some" refers to one or more. All structural and functional equivalents of the elements of the various configurations described throughout this document that are known or will later become known to those skilled in the art are expressly incorporated herein by reference and are intended to be covered by the technology in question. Furthermore, nothing described herein is intended to be dedicated to the public, regardless of whether such a description is explicitly mentioned in the preceding description. While certain aspects and implementations of the technology in question have been described, these have been presented only as examples and are not intended to limit the scope of the technology. In fact, the novel methods and systems described herein can be incorporated in a variety of other ways without departing from their spirit. The appended claims and their equivalents are intended to cover those forms or modifications that would fall within the scope and spirit of the technology in question. It is hereby stated that, as of this date, the best method known to the applicant for putting the aforementioned invention into practice is the one that is clear from the present description of the invention.

Claims

1. An infusion pump, characterized in that it comprises: a housing including an elastic component formed by a single-layer membrane configured to expand and store potential energy generated by the fluid within the infusion pump, and a first tube fluidly coupled to an outlet of the housing, the first tube being configured to conduct the fluid from the housing at a first flow rate based, at least in part, on the potential energy stored by the elastic component and an inside diameter of the first tube, wherein the first flow rate is configured to substantially prime the infusion pump; an air filter fluidly coupled to a distal end of the first tube through an air filter inlet, the air filter being configured to expel air from the fluid through one or more air outlets, wherein the air is expelled substantially upstream, so that the fluid leaving the air filter is air-primed;a second tube fluidly coupled to the air filter via an outlet of the air filter, wherein: the second tube is configured to adjust the first flow rate of the fluid conducted from the housing, through the first tube, to a second flow rate lower than the first flow rate, the second flow rate being based, at least in part, on an inside diameter of the second tube, and an outlet of the second tube is configured to fluidly couple to one or more components for distributing the fluid to a user.

2. The infusion pump according to claim 1, characterized in that the inner diameter of the second tube is not greater than 0.0075 inches (0.1905 mm).

3. The infusion pump according to any of the preceding claims, characterized in that the second tube has a predetermined length and the second flow rate is further based on the predetermined length.

4. The infusion pump according to any of the preceding claims, characterized in that the inner diameter of the first tube and the inner diameter of the second tube are equal.

5. The infusion pump according to any of claims 1 to 3, characterized in that the inner diameter of the first tube and the inner diameter of the second tube are different.

6. The infusion pump according to any of the preceding claims, characterized in that it further comprises a flow restrictor component within the first tube, wherein the flow restrictor component has a smaller diameter than the inside diameter of the first tube.

7. The infusion pump according to claim 6, characterized in that the flow restricting component is a pin configured to change the shape of the fluid from a cylindrical shape to a toroidal shape, wherein: the pin has a predetermined radius, and the first flow rate is further based, in part, on the predetermined radius of the pin.

8. The infusion pump according to any of claims 6 and 7, characterized in that the flow-restricting component is a pin configured to change the shape of the fluid from a cylindrical shape to a toroidal shape, wherein: the pin has a predetermined length, and the first flow rate is further based, in part, on the predetermined length of the pin.

9. The infusion pump according to any of claims 6 to 8, characterized in that the flow-restricting component is one or more rigid beads configured so that the fluid moves around the diameter of one or more rigid beads, wherein: the first flow rate is further based, in part, on the diameter of one or more rigid beads, and one or more rigid beads do not cause the first tube to expand while the fluid moves around the diameter of one or more rigid beads.

10. The infusion pump according to claim 9, characterized in that at least two rigid beads are included in the first tube.

11. The infusion pump according to any of claims 6 to 10, characterized in that the flow restrictor component is not fixed within the first tube and is configured to move a length of the first tube.

12. The infusion pump according to any of claims 6 to 10, characterized in that the flow restrictor component is fixed within the first tube and configured to remain in a predetermined location of the first tube.

13. The infusion pump according to any of the preceding claims, characterized in that the outlet of the second tube is a fixed male luer.

14. The infusion pump according to any of the preceding claims, characterized in that the air filter includes a membrane filter configured to remove one or more contaminants and particles from the fluid.

15. The infusion pump according to any of the preceding claims, characterized in that it further comprises an external flow restrictor coupled to an outer portion of the first tube, the external flow restrictor being configured to provide or remove external pressure to the first tube, respectively closing or opening a fluid passage of the first tube.

16. The infusion pump according to any of the preceding claims, characterized in that it further comprises a controller microcircuit configured to operate a valve to control the first flow of the fluid.

17. The infusion pump according to any of the preceding claims, characterized in that the second flow rate does not exceed 5 mL / h.

18. The infusion pump according to any of the preceding claims, characterized in that one or more components configured to connect to the outlet of the second tube include a skin patch, a needle, and a catheter.

19. The infusion pump according to any of the preceding claims, characterized in that: the housing includes an inlet for receiving the fluid, the fluid received through the inlet expands the elastic component and generates the potential energy stored by the elastic component.

20. The infusion pump according to claim 19, characterized in that the single-layer membrane is a liquid injection molded silicone elastomer membrane. RfrCfr Ln / Zznz / E / YIAI 21. The infusion pump according to any of the preceding claims, characterized in that the elastic component is configured to expand to contain a volume of at least 50 mL of the fluid.

22. The infusion pump according to any of the preceding claims, characterized in that: the housing includes: a first part comprising a first and a second surface, wherein: the first surface includes the outlet of the housing for distributing the fluid, and the second surface, opposite the first surface, includes the elastic component coupled between a first ring and a second ring fixed to the second surface; a second part configured to house the second surface of the first part, wherein the first part and the second part are coupled.

23. A method for infusing fluid to a patient using an infusion pump comprising a housing that includes an elastic component formed by a single-layer membrane, a first tube fluidly coupled to the housing via an outlet of the housing, an air filter fluidly coupled to a distal end of the first tube via an air filter inlet, a second tube fluidly coupled to the air filter via an air filter outlet, and an outlet of the second tube fluidly coupled to one or more components, characterized in that it comprises: receiving a fluid through an inlet of the housing such that the elastic component expands with the fluid and generates potential energy to be stored by the elastic component;to conduct, from the first tube, the fluid from the housing at a first flow rate based, in part, on the potential energy stored by the elastic component and an inside diameter of the first tube, wherein the first flow rate is configured to substantially prime the infusion pump; to expel air from the fluid through one or more vent holes of the air filter, wherein the air is expelled substantially upstream, so that the fluid leaving the air filter is primed air-free; to adjust the first flow rate of the fluid conducted from the housing, through the first tube, to a second flow rate lower than the first flow rate, the second flow rate being based, at least in part, on an inside diameter of the second tube; and to distribute the fluid to a patient through one or more components.

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