Patent Application
20240110551
Apparatuses and methods consistent with example embodiments relate to a pump suitable for subcutaneous delivery of a liquid pharmaceutical product, and more particularly, to a hard seal, compact, positive displacement pump with a reciprocating motion.
Diabetes is a group of diseases characterized by high levels of blood glucose resulting from the inability of diabetic patients to maintain proper levels of insulin production when required. Diabetes can be dangerous to the affected patient if it is not treated, and it can lead to serious health complications and premature death. However, such complications can be minimized by utilizing one or more treatment options to help control the diabetes and reduce the risk of complications.
The treatment options for diabetic patients include specialized diets, oral medications and/or insulin therapy. An effective method for insulin therapy and managing diabetes is infusion therapy or infusion pump therapy in which an insulin pump is used. An insulin delivery device (IDD) may include an insulin pump that can provide continuous infusion of insulin to a diabetic patient at varying rates in order to more closely match the functions and behavior of a properly operating pancreas of a non-diabetic person that produces the required insulin, and the insulin pump can help the diabetic patient maintain his/her blood glucose level within target ranges based on the diabetic patient's individual needs. Infusion pump therapy requires an infusion cannula, typically in the form of an infusion needle or a flexible catheter, that pierces the diabetic patient's skin and through which infusion of insulin takes place. Infusion pump therapy offers the advantages of continuous infusion of insulin, precision dosing, and programmable delivery schedules.
Currently, there are two principal modes of daily insulin therapy for the treatment of type 1 diabetes. The first mode includes syringes and insulin pens that require a needle stick at each injection, typically three to four times per day that are simple to use and relatively low in cost. Another widely adopted and effective method of treatment for managing diabetes is the use of an insulin pump. Insulin pumps can help the user keep blood glucose levels within target ranges based on individual needs, by continuous infusion of insulin. By using an insulin pump, the user can match insulin therapy to lifestyle, rather than matching lifestyle to how an insulin injection is working for the user.
Conventional insulin pumps are capable of delivering rapid or short-acting insulin 24 hours a day through a catheter placed under the skin. Insulin doses are typically administered at a basal rate and in a bolus dose. Basal insulin is delivered continuously over 24 hours, and keeps the user's blood glucose levels in a consistent range between meals and overnight. Some insulin pumps are capable of programming the basal rate of insulin to vary according to the different times of the day and night. Bolus doses are typically administered when the user takes a meal, and generally provide a single additional insulin injection to balance the carbohydrates consumed. Some conventional insulin pumps enable the user to program the volume of the bolus dose in accordance with the size or type of the meal consumed. Conventional insulin pumps also enable a user to take in a correctional or supplemental bolus of insulin to compensate for a low blood glucose level at the time the user is calculating a meal bolus.
There are many advantages of conventional insulin pumps over other methods of diabetes treatment. Insulin pumps deliver insulin over time rather than in single injections and thus typically result in less variation within the blood glucose range that is recommended by the American Diabetes Association. Conventional insulin pumps also reduce the number of needle sticks which the patient must endure, and make diabetes management easier and more effective for the user, thus considerably enhancing the quality of the user's life.
A major disadvantage of existing insulin pumps is that, in spite of their portability, they include multiple components and can be heavy and cumbersome to use. They are also typically more expensive than other methods of treatment. From a lifestyle standpoint, the conventional pump with its associated tubing and infusion set can be inconvenient and bothersome for the user.
Unlike a conventional infusion pump, a patch pump is an integrated device that combines most or all of the fluidic components, including the fluid reservoir, pumping mechanism and a mechanism for automatically inserting the cannula, in a single housing which is adhesively attached to an infusion site on the patient's skin, and does not require the use of a separate infusion or tubing set. Some patch pumps wirelessly communicate with a separate controller (as in one device sold by Insulet Corporation under the brand name OmniPod®), while others are completely self-contained. Such devices are replaced on a frequent basis, such as every three days, when the insulin supply is exhausted.
As a patch pump is designed to be a self-contained unit that is worn by the diabetic patient, it is preferable to be as small as possible so that it does not interfere with the activities of the user. In order to minimize discomfort to the user, it is preferable to minimize the overall dimension of the patch pump. However, in order to minimize the overall dimensions of the patch pump, its constituent parts should be reduced in size as much as possible.
Additionally, the pump, and all other portions of a patch pump or other insulin delivery device (IDD) which come into contact with the fluid or fluid path therein must be subject to sterilization. However, sterilization and ageing can drastically change the properties of elastomeric materials, and pumps utilize an elastomeric material such as liquid silicon rubber (LSR). The use of LSR in the fluid path has been shown to potentially degrade some drug formulations.
Example embodiments may address at least the above problems and/or disadvantages and other disadvantages not described above. Also, example embodiments are not required to overcome the disadvantages described above, and may not overcome any of the problems described above.
According to an aspect of an example embodiment, a positive displacement pump comprises: a housing; a sleeve disposed radially within the housing, wherein an outer conical shape of a first end of the sleeve contacts a conical inner shape of a first end of the housing, thereby sealing the first end of the sleeve to the first end of the housing; and a piston, disposed radially within the sleeve. An axially-reciprocating motion of the piston within the sleeve opens and closes a pump chamber defined between a first end of the piston and a plug disposed within the first end of the sleeve.
The pump may further comprise a cap closing a second end of the housing; and a spring, disposed between the cap and a second end of the sleeve, wherein a pressure of the spring between the cap and the housing biases the sleeve toward the first end of the housing.
The pump may further comprise a piston seal disposed at the first end of the piston, and a plug seal disposed at an end of the plug, wherein the piston seal and the plug seal define the pump chamber therebetween.
The pump may further comprise a helical slot formed in the sleeve; and a pin extending radially outward from the piston, wherein the pin is moveable within the slot, thereby controlling a movement of the piston in radial and axial directions.
The housing and the sleeve may be made of polypropylene.
The pump may further comprise an inlet port and an outlet port formed through the housing.
According to an aspect of another example embodiment, a positive displacement pump comprises: a housing; a sleeve disposed radially within the housing, wherein an outer shape of the sleeve contacts an inner shape of the housing, thereby sealing the sleeve within the housing; and a piston, disposed radially within the sleeve, wherein an wherein an axially-reciprocating motion of the piston within the sleeve opens and closes a pump chamber defined between a first end of the piston and a first end of the sleeve.
The pump may further comprise: a helical slot formed in the sleeve and the housing; and a pin extending radially outward from the piston, wherein the pin is moveable within the slot, thereby controlling a movement of the piston in radial and axial directions.
The sleeve may be rotationally moveable within the housing.
The housing and the sleeve may be made of polypropylene.
The pump may further comprise an inlet port and an outlet port formed through the housing.
According to an aspect of another example embodiment, a fluid delivery system comprises: a reservoir; a cannula; and a pump according to one of the example embodiments described above. The inlet port of the pump is in fluid communication with the reservoir and the outlet port of the pump is in fluid communication with the cannula.
The above and/or other example aspects and advantages will become apparent and more readily appreciated from the following description of example embodiments, taken in conjunction with the accompanying drawings in which:
Reference will now be made in detail to example embodiments which are illustrated in the accompanying drawings, wherein like reference numerals refer to like elements throughout. In this regard, the example embodiments may have different forms and may not be construed as being limited to the descriptions set forth herein.
It will be understood that the terms “include,” “including,” “comprise,” and/or “comprising,” when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof.
It will be further understood that, although the terms “first,” “second,” “third,” etc., may be used herein to describe various elements, components, regions, layers and/or sections, these elements, components, regions, layers and/or sections may not be limited by these terms. These terms are only used to distinguish one element, component, region, layer or section from another element, component, region, layer or section.
As used herein, the term “and/or” includes any and all combinations of one or more of the associated listed items. Expressions such as “at least one of,” when preceding a list of elements, modify the entire list of elements and do not modify the individual elements of the list. In addition, the terms such as “unit,” “-er (-or),” and “module” described in the specification refer to an element for performing at least one function or operation, and may be implemented in hardware, software, or the combination of hardware and software.
Various terms are used to refer to particular system components. Different companies may refer to a component by different names—this document does not intend to distinguish between components that differ in name but not function.
Matters of these example embodiments that are obvious to those of ordinary skill in the technical field to which these example embodiments pertain may not be described here in detail.
One or more example embodiments describe may utilize a hard seal which removes the potentially destabilizing elastomeric material, such as LSR, from the fluid path. An interlock may also be omitted from the pump in order to make the pump smaller, with a lower part count, thereby making it easier to assemble and install. One or more example embodiments may also improve the fit of a drive cross-pin in the piston and resize related components to avoid dosing errors. The helix may be mirrored/reversed in order that the cross-pin may contact on two, opposite sides, balancing loads and kinematic motion, leading to an improved dose accuracy and more stable operation.
A microcontroller 10 may take the form of a printed circuit board (PCB) which interfaces with sensors and circuitry 11, 12, 13, 14, 15, 17 and with actuators 16 and 18, to control the pump and cannula. Power is provided by one or more batteries 19 in the housing. Audible feedback and visual display and user operable controls (not shown) may be provided on the unit, operatively connected to the PCB, or on a remote programming unit, to set dosage, deploy the cannula, initiate infusion and deliver bolus dosages.
The housing has an inlet port 211 therein, in fluid communication with a fluid path from the reservoir 120 to the pump 200, and an outlet port 212 therein, in fluid communication with a fluid path from the pump 200 to the cannula 122. Within the pump 200, the inlet port 211 and outlet port 212 may communicate with a pump chamber 245 inside the sleeve 220, based on a position of the piston 230. The ports 211, 212 may be chamfered to improve an alignment overlap, and one or more switches (not shown) may be placed onto the pump 200 to detect limits of motion to reverse the motor rotation. Within the sleeve, the pump chamber 245 is bounded by a plug seal 241, on a side of the plug 240, and a piston seal 242, on a side of the piston 230. The plug 240 itself may be glued to the sleeve 220 in assembly and rotates with the sleeve 220.
A cross-pin 231 extends radially outward from the piston 230, and moves within a helical slot 221 in the sleeve 220. The sleeve 220 is fixed within the housing 210 both rotationally and axially. A rotation of the piston 230 moves the pin 231 within the slot 221, which is formed helically around the sleeve. With respect to this example aspect, the slot 221 is helical. However, as discussed above, the sleeve and housing may be other than conical, and accordingly, the slot may be other than helical, as would be understood by one of skill in the art. Thus, as the piston 230 rotates, the pin 231 moves within the slot 221, causing the piston 230 to also move towards and away from the plug 240, moving the piston seal 242, and opening and closing the pump chamber 245. The piston 230 may have a flat tab 235 on one end, as shown in
The plug 240 may include a handle 246 which rotates and moves with the pin 231, in order to trigger a switch (not shown) which detects the angular position of the plug 240.
According to this example embodiment, the components of the sleeve 220 and the housing 210 are formed of hard plastic and are held together by pressure sufficient to hold during rotation and after sterilization and aging. The hard plastic may be Vespel or polypropylene, as would be understood by one of skill in the art.
The pump 200 may be driven by a stepper motor (not shown) between a first angular position and a second angular position, respectively representing the two extreme positions of the piston in normal operation. When the pump 220 moves from a first position to an open position, the pump chamber 245 opens, and is in communication with the inlet port 211, pulling fluid from the reservoir 120 into the pump chamber 245. When the pump 200 moves from the open position to a second position, the pump chamber 245 closes, and is in communication with the outlet port 212, pumping the fluid into the outlet port 212 toward the cannula 122.
A dual cross-pin 331 extends radially outward, in opposite directions, from the piston 330, and moves within a slot 321 in the sleeve 320 and the housing 310, as shown in
The piston 330 may rotate and move axially within the sleeve 320. A rotation of the piston 330 moves the pin 331 within the slot 321 in the sleeve 320 and the housing 310. In an inlet closed position, the piston is pressed against the end of the housing 310, closing the pump chamber 345, and the sleeve 320 is rotated such that the sleeve port 346 is in communication with the inlet port 311. As the piston 330 moves from the inlet closed position to an inlet open position, the piston is pulled away from the pump chamber 345, opening the pump chamber 345, and pulling fluid into the pump chamber 345 from the reservoir 120. The sleeve 320 is then rotated from a position in which the sleeve port 346 is in communication with the inlet port 311 to a position in which the sleeve port 346 is in communication with the outlet port 312. The piston 330 then moves from an outlet open position to an outlet closed position, the rotation of the piston 330 moving the piston to close the pump chamber 345, pumping fluid from the pump chamber 345 to the cannula 122. When the piston 330 is in the closed position, the sleeve 320 is then switched again from a position in which the sleeve port 346 is in communication with the outlet port 312 to a position in which the sleeve port 346 is in communication with the inlet port 311.
According to this example embodiment, the components of the sleeve 320 and the housing 310 are formed of hard plastic and are held together by pressure sufficient to hold during rotation and after sterilization and aging.
As with the first example embodiment, the pump 300 may be driven by a stepper motor (not shown).
It may be understood that the example embodiments described herein may be considered in a descriptive sense only and not for purposes of limitation. Descriptions of features or aspects within each example embodiment may be considered as available for other similar features or aspects in other example embodiments.
While example embodiments have been described with reference to the figures, it will be understood by those of ordinary skill in the art that various changes in form and details may be made therein without departing from the spirit and scope as defined by the following claims.
This application claims the benefit of U.S. Provisional Application 63/143,451, filed Jan. 29, 2021 and PCTUS2022014228 filed Jan. 28, 2022, the entire contents of which is hereby incorporated by reference.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2022/014228 | 1/28/2022 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 63143451 | Jan 2021 | US |
