|Publication number||US20050171512 A1|
|Application number||US 10/904,960|
|Publication date||Aug 4, 2005|
|Filing date||Dec 7, 2004|
|Priority date||Sep 8, 2000|
|Also published as||CA2421133A1, CA2421133C, CA2771723A1, CN1471413A, DE60128826D1, DE60128826T2, EP1335764A2, EP1335764B1, US6740059, US7029455, US7137964, US20020072733, US20030097092, US20040087894, WO2002020073A2, WO2002020073A3|
|Publication number||10904960, 904960, US 2005/0171512 A1, US 2005/171512 A1, US 20050171512 A1, US 20050171512A1, US 2005171512 A1, US 2005171512A1, US-A1-20050171512, US-A1-2005171512, US2005/0171512A1, US2005/171512A1, US20050171512 A1, US20050171512A1, US2005171512 A1, US2005171512A1|
|Original Assignee||Insulet Corporation|
|Export Citation||BiBTeX, EndNote, RefMan|
|Referenced by (83), Classifications (20), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The present application is a continuation of U.S. patent application Ser. No. 10/695,547, filed Oct. 28, 2003, which is a continuation of U.S. patent application Ser. No. 09/943,992, filed Aug. 31, 2001, now U.S. Pat. No. 6,740,059, which claims priority to provisional U.S. patent application Ser. No. 60/231,476, filed on Sep. 8, 2000. All of these applications are assigned to the assignee of the present application and incorporated herein by reference.
The present disclosure relates generally to medical devices, systems and methods, and more particularly to small, low cost, portable infusion devices and methods that are useable to achieve precise, sophisticated, and programmable flow patterns for the delivery of therapeutic liquids to a patient.
Today, there are many diseases and other physical ailments that are treated by various medicines including pharmaceuticals, nutritional formulas, biologically derived or active agents, hormonal and gene based material and other substances in both solid or liquid form. In the delivery of these medicines, it is often desirable to bypass the digestive system of a patient to avoid degradation of the active ingredients caused by the catalytic enzymes in the digestive tract and liver. Delivery of a medicine other than by way of the intestines is known as parenteral delivery.
Parenteral delivery of various drugs in liquid form is often desired to enhance the effect of the substance being delivered, insuring that the unaltered medicine reaches its intended site at a significant concentration. Also, undesired side effects associated with other routes of delivery, such as systemic toxicity, can potentially be avoided by parenteral delivery. Parenteral delivery of liquid medicines may best be accomplished by infusing directly into the cardiovascular system via veins or arteries, into the subcutaneous tissue or directly into organs, tumors, cavities, bones or other site specific locations within the body.
Parenteral delivery is often accomplished by administering bolus injections using a needle and syringe, or continuously by gravity driven dispensers or transdermal patch technologies. Bolus injections often imperfectly match the clinical needs of the patient, and usually require larger individual doses than are desired at the specific time they are given. Continuous delivery of medicine through gravity feed systems compromise the patient's mobility and lifestyle, and limit the therapy to simplistic flow rates and profiles. Transdermal patches have special requirements of the medicine being delivered, particularly as it relates to the molecular structure, and similar to gravity feed systems, the control of the drug administration is severely limited.
Ambulatory infusion pumps have been developed for delivering liquid medicaments to a patient. These infusion devices have the ability to offer sophisticated fluid delivery profiles accomplishing bolus requirements, continuous infusion and variable flow rate delivery. These infusion capabilities usually result in better efficacy of the drug and therapy and less toxicity to the patient's system. An example of a use of an ambulatory infusion pump is for the delivery of insulin for the treatment of diabetes mellitus. These pumps can deliver insulin on a continuous basal basis as well as a bolus basis.
The ambulatory pumps often work with a reservoir to contain the liquid medicine, such as a cartridge or syringe, and use electromechanical pumping or metering technology to deliver the medication to the patient via tubing from the infusion device to a needle that is inserted transcutaneously, or through the skin of the patient. The devices allow control and programming via electromechanical buttons or switches located on the housing of the device, and accessed by the patient or clinician. The devices include visual feedback via text or graphic screens, such as liquid crystal displays (LCD), and may include alert or warning lights and audio or vibration signals and alarms. The devices can be worn in a harness or a pocket, or strapped to the body of the patient.
Currently available ambulatory infusion devices are expensive, difficult to program and prepare for infusion, and tend to be bulky, heavy and very fragile. Filling these devices or their reservoirs can be difficult and require the patient to carry both the intended medication as well as filling accessories when traveling or even just going to work. The accuracy and safety requirements of these devices are extremely important, based both on the medicine being delivered and the condition of the patient. Therefore, the devices require specialized care, maintenance and cleaning to assure proper functionality and safety for their intended long term use.
Clearly, therefore, there is a need for a programmable and adjustable infusion system that is precise and reliable and can offer clinicians and patients a small, low cost, light weight, simple-to-use alternative for parenteral delivery of liquid medicines.
The applicant has determined that a sophisticated ambulatory infusion device that can be programmed to reliably deliver variable flow profiles of liquid medications, yet is small, light weight and low cost, is needed. Smaller and lighter devices are easier to carry and are more comfortable for the patient, even allowing the device to be adhesively attached to the patient's skin similar to a transdermal patch. An inexpensive device allows greater flexibility in prescribing the device for use by reducing the financial burden on healthcare insurance providers, hospitals and patient care centers, as well as patients themselves. In addition, low cost devices make more practical the maintenance of one or more replacement devices. If the primary device is lost or becomes dysfunctional, availability of the replacement avoids costly expedited repair and down time.
Aspects of the present disclosure will enable cost reductions significant enough to make the entire device disposable in nature, being replaced as frequently as every two to five days. A disposable device allows the medication to be prefilled by the manufacturer and does not need the routine cleaning and maintenance required by long term devices, greatly simplifying use for the patient.
The present disclosure, therefore, provides a method for transcutaneously delivering fluid to a patient, which includes providing at least one disposable infusion pump. The disposable infusion pump is provided with a housing adapted to be mounted on a patient's skin, a transcutaneous patient access tool for extending through the housing and providing transcutaneous access to the patient, a reservoir prefilled with a therapeutic fluid, and a dispenser for causing fluid from the reservoir to flow to the transcutaneous patient access tool. The disposable infusion pump is also provided with a processor connected to the dispenser and programmed to cause a flow of fluid from the reservoir to the transcutaneous patient access tool based on flow instructions, and a wireless receiver connected to the processor for receiving flow instructions from a remote controller and for delivering the flow instructions to the processor.
The method further includes placing the disposable infusion pump on a patient's skin, receiving flow instructions from a remote controller through the wireless receiver of the infusion pump, and delivering the flow instructions to the processor of the infusion pump, so that the processor causes fluid from the reservoir to flow to the transcutaneous patient access tool based on the flow instructions.
According to one aspect of the present disclosure, the methods also includes the step of remotely supplying flow instructions to each of the disposable infusion pumps through a reusable remote control device.
These aspects of the disclosure together with additional features and advantages thereof may best be understood by reference to the following detailed descriptions and examples taken in connection with the accompanying illustrated drawings.
Like reference characters designate identical or corresponding components and units throughout the several views.
Set forth hereinbelow are detailed descriptions of exemplary embodiments of fluid delivery devices, systems and kits, constructed in accordance with the present disclosure, as well as methods for using the devices, systems and kits. The types of liquids that can be delivered by the fluid delivery devices, systems and kits of the present disclosure include, but are not limited to, insulin, antibiotics, nutritional fluids, total parenteral nutrition or TPN, analgesics, morphine, hormones or hormonal drugs, gene therapy drugs, anticoagulants, analgesics, cardiovascular medications, AZT or chemotherapeutics. The types of medical conditions that the fluid delivery devices, systems and kits of the present disclosure might be used to treat include diabetes, cardiovascular disease, pain, chronic pain, cancer, AIDS, neurological diseases, Alzheimer's Disease, ALS, Hepatitis, Parkinson's Disease or spasticity.
In the exemplary embodiment of
The local processor 50 contains all the computer programs and electronic circuitry needed to allow a user to program the desired flow patterns and adjust the program as necessary. Such circuitry can include one or more microprocessors, digital and analog integrated circuits, resistors, capacitors, transistors and other semiconductors and other electronic components known to those skilled in the art. The local processor 50 also includes programming, electronic circuitry and memory to properly activate the dispenser at the needed time intervals. In the exemplary embodiment of
When the local processor 50 activates the dispenser 40, a specific amount of fluid exits the fluid delivery device 10 via the exit port assembly 70. The exit port assembly 70 can include elements to transcutaneously enter the patient, such as a needle or soft cannula, or can be adapted to connect to a standard infusion device that includes transcutaneous delivery means.
As shown, the housing 20 is free of user input components for providing flow instructions to the local processor 50, such as electromechanical switches or buttons on an outer surface 21 of the housing, or interfaces otherwise accessible to a user to adjust the programmed flow rate through the local processor 50. In order to program, adjust the programming of, or otherwise communicate user inputs to the local processor 50, the fluid delivery device 10 includes the wireless communication element, or receiver 60 for receiving the user inputs from a separate, remote control device, such as the separate, remote control device 100 of
The remote control device 100 has user input components, including an array of electromechanical switches, such as the membrane keypad 120 shown. The control device 100 also includes user output components, including a visual display, such as a liquid crystal display (LCD) 110. Although not shown in
A user, such as a patient or a clinician, can thus program the fluid delivery device 10 by entering information into the remote control device 100, which then downloads information to the receiver 60 of the device 10 with each key stroke or button pressed or in a batch mode of multiple key strokes. Complex flow algorithms, requests for bolus delivery and other desired infusions of the medicinal fluid can be accomplished by entering information into the remote control device 100, which is then transmitted to the fluid delivery device 10. The communication can be confirmed as acceptable by the local processor 50 of the fluid delivery device 10 by using one or more features such as standard handshaking protocols, redundant transmissions and other communication confirmation methods, as are known to those skilled in the art.
The lack of user interfaces, such as electromechanical switches on the fluid delivery device 10, results in substantial reductions in the cost, the size, and the weight of the device 10. The lack of user interfaces also allows the housing outer surface 21 of the device 10 to be relatively smooth, thereby simplifying cleaning and preventing jewelry or clothing items such as sweaters from catching on the device. Since the remote control device 100 also includes a visual display 110, the fluid delivery device 10 can be void of an information screen, further reducing cost, size and weight. Lack of user interfaces, such as electromechanical switches and information screens, greatly simplifies the design of the fluid delivery device 10 and allows the device 10 to be made more flexible and resistant to damage.
Alternatively, the housing 20 may include a flexible cantilever beam that contacts the reservoir 30 creating a pressure within the reservoir 30 above atmospheric pressure. In another alternative, the reservoir chamber 35 may be sealed and filled with a gas, or a vapor-plus-fluid mixture, to place the fluid within the reservoir 30 under pressure above atmospheric pressure. The gas can be air, and the vapor-plus-fluid mixture can be Freon. The Freon vapor-plus-fluid mixture provides the design advantage of near constant pressure if the fluid delivery device 10 is maintained at near constant temperature. In still another alternative embodiment, the amount of gas placed in a sealed reservoir chamber 35 may be chosen such that the reservoir 30 pressure is equal to or less than atmospheric for the entire full to empty conditions of the reservoir 30. If the fluid in the reservoir 30 is maintained at a pressure equal to or below atmospheric, then the dispenser 40 is provided in the form of a pump, such as a peristaltic drive pump, for pumping fluid from the reservoir 30 to the outlet port assembly 70.
The reservoir 30 may be prefilled by the device manufacturer or a cooperating drug manufacturer, or may include external filling means consisting of a fill assembly 31. If the fluid delivery device 10 is prefilled by the manufacturer, the local processor 50 can be provided with memory containing various information regarding the prefilled drug including but not limited to, the type or name and the concentration and volume of the fluid.
The fill assembly 31 can include a needle insertion septum 32. The reservoir 30 and other fluid path components may be placed in a vacuum during the final manufacturing process to simplify filling and priming of the fluid delivery device 10 for the patient. Needle insertion septum 32 may be constructed of a resealing elastomer such as silicone that allows a needle to puncture septum to add fluid to the reservoir 30, yet reseal after the needle is withdrawn. An alternative to the needle insertion septum 32 is a standard fluid connection, such as a Luer connector, which can be affixed to the fill assembly 31 in combination with a one way valve such as a duck bill valve (not shown). The patient could attach a syringe filled with the liquid medication to the Luer connector and fill the fluid delivery device 10. The fill assembly 31 may be designed so that the patient can fill the fluid delivery device 10 one time only, such as by having the Luer connection break off when the syringe is removed.
The dispenser 40 is connected in fluid communication with the reservoir 30. When the device 10 is provided with a pressurized reservoir 30, as shown in exemplary embodiment of
The dispenser 40 of the exemplary embodiment of
The inlet valve 41 and the outlet valve 42 of the dispenser 40 and the local processor 50 are designed to prevent both valves from being opened at the same time, precluding the reservoir 30 to ever flow directly to the exit port assembly 70. The prevention of both valves opening at the same time is critical and can be accomplished via mechanical means, electrical means, or both. The prevention can be accomplished in the dispenser 40 design, the local processor 50 design, or both.
The dispenser 40 shown in
The PV may not always be constant enough to be within the accuracy requirements of the fluid delivery device 10. One factor impacting the PV is reservoir pressure. The fluid delivery device 10 may include means for monitoring reservoir pressure (RP) and adjust the timing between pulses to achieve the desire flow pattern. An example of such compensation would be to decrease time between pulses as the PV decreases to maintain the programmed flow rate. Means for monitoring such parameters as reservoir pressure RP are described below. An alternative to monitoring reservoir pressure is monitoring the volume of the reservoir 30. Each time a pulse or series of pulses are delivered, a measurement of reservoir volume can indicate whether a proper amount of fluid has been delivered, both for individual pulses and cumulative pulses. The system could also be designed to compensate fluid flow as errors are detected. An example of a reservoir volume transducer means is also described below.
The communication element 60 preferably receives electronic communication from the remote control device 100 using radio frequency or other wireless communication standards and protocols. The information transferred includes codes or packets of codes that the local processor 50 uses to confirm that the information was received correctly, similar to the way standard telephone modem communication is performed. More sophisticated codes can be included to allow the information to be self-corrected or pinpoint the area of bad information. In an even more preferred embodiment, the communication element 60 is a two-way communication element, including a receiver and a transmitter, for allowing the fluid delivery device 10 to send information back to the remote control device 100. In such an embodiment, the remote control device 100 also includes an integral communication element 60 comprising a receiver and a transmitter, for allowing the remote control device 100 to receive the information sent by the fluid delivery device 10.
The power supply 80 can be integrated into the fluid delivery device 10 and not accessible to a user. In an alternative embodiment, however, the power supply 80 can be replaceable, e.g., a replaceable battery. In another embodiment, the power supply 80 can comprise an integrated battery or capacitor, for low power components of the device 10 such as the electronic memory, and a user-inserted battery for powering the remainder of the device 10. Other components that may require electrical energy are the communication element 60, the dispenser 40, and other components such as sensors or transducers.
As shown in
Since the fluid delivery device 10 may be worn close to or even attached to the body of a mammalian patient, it may be desired to prevent the temperature of the fluid in the reservoir 30 from elevating toward the body temperature of the patient. In one embodiment, the reservoir chamber 35 can be sealed and placed in a vacuum, similar to construction of a thermos bottle. The internal surface of the reservoir chamber 35 can be coated with reflective material, also similar to a thermos bottle. Alternatively, the chamber 35 can be filled with insulating material such as a low thermal conductance foam, with sufficient cavity size to allow the reservoir 30 to expand to a maximum fill capacity. Shown in
The second reservoir 90 may be filled with a drug different from the drug in the main reservoir 30, a diluent of the drug in the main reservoir 30 or any inert substance. The fluid from the additional reservoir 90 may be administered to dilute the fluid dispensed from the main reservoir 30, to provide more sophisticated or additive therapies, or even to maintain patency of the transcutaneous fluid path by flowing an inert substance at a more frequent rate then the intended infusion of the fluid in the main reservoir 30.
Referring also to
The device 10 further includes an adhesive layer 201 on the outer surface 21 of the housing 20 for securing the device 10 directly to the skin of a patient. The adhesive layer is preferably provided in a continuous, oval shape encircling the exit port assembly 70 in order to provide a protective seal around the penetrated skin. The housing adhesive layer 201 can consist of material such as that used in bandages or electro surgery return pads such as those manufactured by the Valley Lab division of Tyco/U.S. Surgical.
A needle connection tubing 73 terminating in a skin penetrating cannula 72 is shown connected to the exit port assembly 70. The needle connection tubing 73 is flexible, allows various placements and can be reinforced to prevent kinking. Reinforcement can be accomplished through choice of materials and ratio of wall thickness to inner diameter, or the tubing 73 can be reinforced with an internal wire coil. The skin penetrating cannula 72 can be a rigid member, such as a needle, or can be flexible. The skin penetrating cannula 72 is inserted through the skin 210 prior to attaching the fluid delivery device 10 to the skin 210 and may be inserted using a needle insertion assistance mechanism. Such a needle insertion assistance mechanism may be integrated into the fluid delivery device 10, or can be supplied as a separate mechanism.
The microcontroller 50 can include a microprocessor 51, memory 52, an electronic clock oscillator 53, an analog-to-digital converter 54 and a multiplexer 55. Also shown in
The device of
As also shown in
In order to deliver a fixed amount of fluid when the bolus button 180 is pressed, a bolus flow restrictor 184 and a bolus volume accumulator 185 are provided in the bolus delivery tubing 186. The bolus flow restrictor 184 acts as a flow limiter to prevent free flow of fluid from the reservoir 30, and creates a minimum lock-out period between full bolus volumes. Assuming in this particular embodiment that the reservoir 30 is maintained at a pressure above atmospheric pressure, the flow rate of the flow restrictor 184 is chosen to be much slower than the rate at which the bolus volume should be delivered.
The bolus volume accumulator 185 expands with the inflow of fluid from the flow restrictor 184 as long as the bolus release finger 183 is occluding the bolus delivery tubing 186. The amount of expansion of the bolus volume accumulator 185 equals the bolus volume to be delivered. When the bolus button 180 is depressed, the bolus volume of fluid maintained in the bolus volume accumulator 185 is dispensed through the bolus delivery tubing lumen 186 and out of the exit port assembly 70.
The time to dispense the bolus dose should be short since there are no downstream flow restrictors, and the user could be instructed to hold the button down for a required time, not more than a few seconds. Alternative designs could latch the bolus button 180 for a specific amount of time only, as the button must be released to prevent continued flow via the flow restrictor 184. After the bolus button 180 is pressed, bolus volume accumulator 185 fluid is delivered until the pressure in bolus volume accumulator 185 reaches atmospheric pressure. Release of bolus button 180 causes the bolus lever 187 to rotate back, pivoting around bolus pivot 182 until bolus release finger 183 is occluding bolus delivery tubing lumen 186 by pressing it against housing button stop 28. Bolus volume accumulator 185 again expands an amount equal to the next bolus volume to be delivered as fluid from reservoir 30 passes through bolus flow restrictor 184 until the pressure in bolus volume accumulator 185 equals the pressure in reservoir 30.
The visual display 110 can also include information such as warning and alarm conditions based on the status of the fluid delivery device 100. Elements such as indicator lights, buzzers, and vibrational alarms may also be included in the remote control device 100 as alternative or redundant means for communicating information to the user.
The user can get information and adjust the programming of the device by depressing various electromechanical switches also mounted on controller housing 102. These switches may be joined in a bank of switches and included in membrane keypad 120 as shown in
The remote control device 100 may include various electromechanical jacks, which can accept electromechanical plugs from various devices. Shown in the figure are three plugs, a bar code reader 140, a glucometer port 150 and a computer port 170. These ports can allow two way transfer of information to enhance the capabilities of remote control device 100 and improve its user friendliness.
The controller communication element 160 is designed to transmit signals, or information to the communication element 60 of the fluid delivery device 10. The controller electronics 105 act as a “translator” in translating user inputs received through the user interfaces 120 into signals for transmission by the controller communication element 160. In a preferred embodiment, both the communication element 60 and the controller communication element 160 are two way communication assemblies allowing two way communication between the remote control device 100 and fluid delivery device 10. In order to send wireless information the communication element 60 and the controller communication element 160 may include inductive wire loops or other transmitting antenna means. Information can be sent using amplitude or frequency modulation, and can be broadcast in the radio frequency, or RF range. Standard information confirmation techniques such as handshaking or checksum protocols can be used to insure accurate information transfer. With two-way communication, when errors are detected, the transfer can be repeated until acceptable, a similar technique to that utilized with two way pager technology commonplace today.
If the fluid delivery device 10 is prefilled prior to patient use, the electronic memory of local processor 50 may contain information regarding the fluid including but not limited to type or name, concentration, amount, volume, additional drugs in solution and any diluting agents. This information can be transmitted from the fluid delivery device 10 via its communication element 60, and uploaded into the remote control device 100 via its controller communication element 160. Other information may be factory installed into the fluid delivery device 10 including but not limited to manufacturing date, expiration date, sterilization date, therapy information such as defined flow profiles and even patient or hospital information. This information can be uploaded into the remote control device 100 as described above, and the remote control device 100 may adjust its internal programming based on the information received.
In a preferred embodiment, the electronic memory of the fluid delivery device 10 includes the latest program of the remote control device 100 available at the time of manufacture of the fluid delivery device 10. Similarly, the electronic memory of the remote control device 100 includes the latest program of the fluid delivery device 10, available at the time of manufacture of the remote control device 100. At the first communication between the remote control device 100 and the fluid delivery device 10, a program check is performed, and if a newer software version for either device is available from the other device, and the existing hardware is compatible, another feature which can be programmed into both devices, the newer program is downloaded into memory and used by the upgraded device. The embedded program may be contained in read only memory, or ROM, while the downloaded program can be written into electronically writeable memory. The automatic update feature, available for each device to upgrade the other, is another way to make sure the user has the best available product for use.
Another advantageous feature associated with two way communication is the addition of a proximity alarm. The design of the fluid delivery device 10 and remote control device 100 electronics can be such that when the distance between the two devices is greater than a particular radial length, one or both of the devices will alert the user, potentially with an audio alarm. The alarming distance should be chosen so that it is less than the maximum communication range of the two devices. A method of creating the alarm is for the fluid delivery device 10 to send out frequent packets of information at a predetermined rate and at an amplitude or power less than the normal communication power, providing a safety margin for the proximity detection. The remote control device 100 is programmed to expect to receive this communication at the predetermined rate, and lack of receipt of one or more of these packets, causes the remote control device 100 to activate its audio alarm 106. Alternatively or additionally, a vibrational alarm may be included. Proximity alarms may be included that do not require two way communication, by integrating a device such as a magnet into the housing 20 of fluid delivery device 10, and integrating magnetic field detection means into the remote control device 100. When the magnetic field detection means of the remote control device 100 do not detect the presence of the magnetic field of the fluid delivery device 10, the remote control device 100 activates the controller audio alarm 106.
The remote control device 100 includes a controller power supply 108 that powers the various electronic components including the controller electronics 105, controller audio alarm 106. The controller power supply 108 may be a standard battery and in the preferred embodiment, the power supply 108 may be replaceable by the user by removing a battery door, not shown, and replacing after power supply 108 is inserted and attached. In an alternative embodiment, the power supply is integrated into the remote control device 100, and can be recharged with a separate device or contains enough power to supply the device for its intended length of use.
The fluid delivery device 10 of the present disclosure may be sold to hospitals, pharmacies, outpatient centers or the patients themselves. If the fluid delivery device is intended for short term or disposable use, it may be practical to sell each device with various accessories or groups of accessories that are convenient for the user. It may be desirable for certain parts of the fluid delivery device, or accessories such as an attachable transcutaneous infusion set, such as that described hereinabove, to be packaged sterilized in a protective packaging. Proper aseptic maintenance of the portion of the skin that receives the transcutaneous access is important to prevent infection. FIGS. 13, 13 a, 13 b and 13 c depict various components that may be packaged together in kit form.
The top of the housing 20, or housing top side 203 includes a housing transparent window 22 located above the reservoir 30. The transparency of the housing transparent window 22 and design of the reservoir 30 are such that the patient can determine information regarding status of the reservoir 30 by viewing through the housing transparent window 22. Such information can include amount of drug remaining or presence of a leak. Alternatively, the entire housing 20 may be transparent yielding similar visual indications.
Also included in the fluid delivery device 10 of this embodiment is an information barcode 26 which can include various pieces of information regarding the status of that particular fluid delivery device 10 such as type, volume and concentration of drug prefilled in the device, expiration date of device or drug, manufacture date of device or drug, serial numbers, lot numbers, hospital name, clinician name, patient name, prescription requirements and various other pieces of information. The barcode information can be read into a hospital or home computer, or in the preferred embodiment is uploaded via a barcode reader integral to the remote control device 100. The fluid delivery device 10 and remote control device 100 electronics and programming can be designed such that the bar code must be read prior to programming or otherwise using the fluid delivery device 10. This feature can greatly reduce programming errors such as those associated with the patient entering drug information. If the patient were to enter a drug concentration that was incorrect, and did all the remaining programming in units of drug, instead of volume, which is common practice, while the device would function properly, all of the volumes delivered would be inaccurate based on the ratio of the incorrect concentration entered versus the true concentration of the drug being delivered. Many drugs are available in multiple concentrations such as insulin often made available to patients in 40, 50 and 100 units per ml concentrations.
The fluid delivery device 10 of the present disclosure is intended to be low cost and potentially disposable. It may be advantageous for one or more of the components to be biodegradable, since replacement of the device every two to five days has many advantages, it would also generate a fair amount of waste. The fluid delivery device 10 may include a preinstalled battery as its power supply 80. In order to prevent the battery from powering the electronics of fluid delivery device 10 before its intended use, a mechanical switch may be included, connecting the battery contacts to the electronics prior to programming with the remote control device 100. A simplistic version of the switch design may be an insulating material between the battery contacts of power supply 80 and the electrical connection to the local processor 50. The insulating material could be designed to protrude through housing 20, and be removable by the user, not shown. The user could pull the insulating material and remove it, simultaneously connecting the battery contacts with the electrical connection to the local processor.
The fluid delivery device 10 of the present disclosure may be filled with the therapeutic fluid by the device manufacture, a pharmaceutical company, or another manufacturer prior to its shipment to the hospital, pharmacy or patient. Certain drugs require refrigeration or other special environmental conditions, requiring the prefilled fluid delivery device to be refrigerated or otherwise handled to meet special requirements. Insulin is a drug that requires refrigeration if it is to be stored for a prolonged period of time. Hoechst, of Frankfurt Germany, is developing insulin that is stable at higher temperatures. Drugs that are stable at room temperature, such as the developmental insulin of Hoechst, allow simple filling and handling of the fluid delivery device 10, greatly simplifying the requirements for the patient.
Various methods of using the fluid delivery device 10 are included in the present disclosure and described above. The method of programming the fluid delivery device 10 with remote programmer 100 as well as the attachment and use of the peripheral devices including transcutaneous infusion sets and diagnostic devices such as glucometers are described. Also relevant is the ability to update the internal programming of either the fluid delivery device 10 or the remote control device 100 by the corresponding device. Methods of filling the fluid delivery device 10 with therapeutic fluid during the manufacturing process as well as by the user have been described. Methods and timing of sterilization and packaging of part or all of the fluid delivery device 10 and therapeutic fluid have also been described.
Although exemplary embodiments of the disclosure have been shown and described, many changes, modifications and substitutions may be made by those having ordinary skill in the art without necessarily departing from the spirit and scope of this disclosure. For example, the fluid delivery device of this disclosure is intended to be low cost, light weight, simple to use and potentially disposable by removing a majority of the user interface, including electromechanical switches, from the fluid delivery device, and including a separate controller to replace those functions. A reservoir, fluid dispenser, transcutaneous fluid administration means, solid state electronics and wireless communications are included in the fluid delivery device to perform its intended function. While various means for reservoir construction, pressurization means, fluid pumping means, fluid metering means, transcutaneous delivery, electronic control and wireless communications have been discussed in this application, alternatives to each of these areas can be made without departing from the spirit of the disclosure.
In addition, where this patent application has listed the steps of a method or procedure in a specific order, it may be possible (or even expedient in certain circumstances) to change the order in which some steps are performed, and it is intended that the particular steps of the method or procedure claims set forth hereinbelow not be construed as being order-specific unless such order specificity is expressly stated in the claim.
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|International Classification||A61K9/22, A61M5/14, A61M37/00, A61M5/00, A61M5/142, A61M5/168|
|Cooperative Classification||A61M2005/1403, A61M2005/14268, A61M2005/1405, A61M5/14248, A61M5/16813, A61M2209/01, A61M2205/50, A61M2205/35, A61M37/00, A61M2205/6072, A61M2205/3569, A61M5/16809|
|Mar 22, 2005||AS||Assignment|
Owner name: INSULET CORPORATION, MASSACHUSETTS
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:FLAHERTY, J. CHRISTOPHER;REEL/FRAME:015806/0154
Effective date: 20020116