HK1189364B

HK1189364B - Medicant delivery system

Info

Publication number: HK1189364B
Application number: HK14102484.3A
Authority: HK
Inventors: Goodman Jack; O'neill William; Chinhak Chong Alexander; P. BARTKOWSKI William; Joseph Kovach Peter; Gawain Linde Larry; Eugene Berg Randy
Original assignee: Cqens Technologies Inc.
Priority date: 2011-04-22
Filing date: 2012-04-23
Publication date: 2017-10-06

Description

Drug delivery system

Technical Field

The present invention relates to a device and method for evaporating a liquid for inhalation. In particular, the present invention relates to providing a device and method for controlling, metering and measuring the precise volume of vaporized fluid and vapor generated by a hand-held vaporization device each time the device is activated by its user, which is more reliable and safer than current devices that rely on lithium ion chemistry.

Background

A variety of hand-held, individualized vaporization devices are currently available. Some of these devices are specifically designed to generate nicotine infused vapor for use as a substitute for a conventional tobacco cigarette, where the tobacco is lit and the user inhales the smoke and its components, including nicotine (a naturally occurring component of tobacco). The device used as a cigarette substitute generates a vapor that is free of more than 4000 compounds of tobacco smoke and most of the constituents of the by-products, thereby delivering nicotine to the user through ingestion of the vapor without the most hazards typically associated with tobacco smoke.

Unfortunately, there are still some drawbacks in the design and performance of these evaporation devices. For example, some devices are bulky or cumbersome and difficult to use as portable, hand-held devices.

Other vaporization devices are not capable of delivering precise, consistent and reliable metered doses of medicament. Current electronic cigarette nebulizers do not provide a means of controlling the consistency of the volume of liquid vaporized or the volume of vapor generated, and therefore do not produce a measurable amount of nicotine on a per vaporization basis. There are also certain situations and situations involving regulatory possible indications where it is likely that these devices are required to be able to deliver a vapour and its nicotine composition in such a way that the amount of nicotine present in the vapour is measurable and consistently repeated with each activation by the user. In addition to or instead of nicotine, the vaporizer may be used to deliver other substances to the user, including drugs. Similarly, a "dose" for these substances that is precisely measured is desirable or even necessary.

Furthermore, since some of the devices on the market use liquid storage units that are "open" to the environment, some devices can leak or fail to operate reliably unless the evaporation device is held in an upright position during use or during packaging, transport and storage of the device. In addition, with such devices, the liquid may be contaminated, adulterated and/or volatilized under certain conditions.

Finally, most, if not all, of the currently available products use lithium chemical batteries as their power source. This is mainly due to three factors: 1) the service life of the battery; 2) the power required to evaporate the fluid; and 3) the need for small compact devices, roughly the size of conventional tobacco products (i.e., cigarettes and cigars), or in non-tobacco or nicotine formulations, the need for compactness for discrete use by the user as the situation permits. However, lithium chemical cells are unstable, hazardous (both because they can release toxic vapors and because under certain conditions explosions can occur), and can also be environmentally hazardous in terms of storage, reliability, and disposal.

With the increasing range of sales and use of current products and as these devices become more used for identification, manufacture, distribution, sale, and consumption, lithium chemical power sources for handheld portable devices are expected to be a problem for us managers, distributors, retailers, and consumers.

Accordingly, there remains a need for a device and method to provide an improved handheld vapor delivery system that reliably and consistently generates repeatable metered doses of medicament in a safe, efficient and effective manner.

Disclosure of Invention

In one aspect, a method and apparatus for retrofitting a handheld vapor delivery device to generate reliable, consistent, repeatable metered doses of a medicament or drug includes a power control system that utilizes an integrated circuit capable of determining and delivering precise amounts of power for precise durations of time just sufficient to completely vaporize a predetermined volume of liquid.

In another aspect, methods and devices for an improved handheld vapor delivery device may include a fluid delivery system, an evaporation or aerosolization system, and a power control system contained in a housing, wherein the fluid delivery system delivers a precisely metered dose to the aerosolization system consistently, repeatably, and reliably, and the power delivery system supplies just enough electrical power to the aerosolization system to completely aerosolize or vaporize a precise volume of liquid delivered to the aerosolization system.

On the other hand, the hand-held vapor delivery device can be operated independently of orientation, and/or can deliver a repeatable dose of medication, and/or can be stored in any orientation, and/or can maximize energy efficiency.

In another aspect, the present invention provides an apparatus and method that enables a vapor delivery device to use a more stable, more reliable, less environmentally hazardous, and safer battery chemistry power source without significantly impacting the portability and discreteness of the device.

Drawings

Fig. 1 is a perspective view of one embodiment of a drug delivery device of the present invention.

Fig. 2 is a top view of the device shown in fig. 1.

Fig. 3 is a sectional view taken along line 3-3 in fig. 2.

Fig. 4 is an enlarged detail sectional view of the upper portion of the device shown in fig. 3.

Fig. 5 is an exploded perspective view of the device shown in fig. 1-4.

Fig. 6 is an enlarged perspective view of the elements of the device shown in fig. 3-5.

Fig. 7 is a perspective view of another embodiment of the present invention with the housing removed for illustration purposes.

Fig. 8 is an exploded perspective view of the embodiment shown in fig. 7.

Fig. 9 is an enlarged side view showing details of the elements shown in fig. 7 and 8.

Fig. 10-13 are side views of the apparatus shown in fig. 7-9 illustrating sequential steps of operation.

Fig. 14 is an enlarged perspective view of the vaporization system shown in fig. 7-9.

Fig. 15 is a schematic diagram of a "one shot" circuit that may be used in one embodiment of the power control system of the present invention.

Fig. 16 and 17 are schematic diagrams of similar modified circuits that may be used in one embodiment of a power control system.

FIG. 18 is an enlarged side view of an embodiment of an evaporation element.

FIG. 19 is a perspective view of another embodiment of an evaporation device.

Fig. 20 is a sectional view of the evaporation apparatus shown in fig. 19.

Fig. 21 is an exploded perspective view of the evaporation apparatus shown in fig. 19 and 20.

Fig. 22 is an enlarged perspective view of the element shown in fig. 20.

Fig. 23 is an isometric view of another embodiment of a drug delivery device.

Fig. 24 is an exploded view of the device shown in fig. 23.

FIG. 25 is a close-up isometric view of one embodiment of the fluid delivery system shown in FIG. 24.

Fig. 26 is a cross-sectional view taken through line 26-26 in the fluid delivery system shown in fig. 25.

FIG. 27 is a close-up isometric view of one embodiment of a plunger of the fluid delivery system shown in FIG. 28.

Fig. 28 is a close-up isometric view of an embodiment of a drive nut of the fluid delivery system shown in fig. 24.

Fig. 29 is a close-up isometric view of one embodiment of the outlet cap and the vaporization system of the drug delivery device of fig. 24.

Fig. 30 is a close-up isometric view of an embodiment of a fluid release actuator of the drug delivery device shown in fig. 24.

Fig. 31A is a close-up isometric view of the proximal end of the fluid delivery system of the drug delivery device shown in fig. 24.

Fig. 31B is the drug delivery device of fig. 31A with the bottom depressed.

Fig. 32 is an isometric view of an embodiment of an anti-rotation feature of the fluid delivery system shown in fig. 24.

Fig. 33 is an isometric view of another embodiment of the delivery device.

Fig. 34 is an isometric view of the delivery device shown in fig. 33 with the housing removed.

FIG. 35 is a close-up view of the top of the delivery device shown in FIG. 33, illustrating the vaporization system.

FIG. 36 is a block diagram of an embodiment of a power control system.

Detailed Description

The detailed description set forth below in connection with the appended drawings is intended as a description of the presently preferred embodiments of the invention, and is not intended to represent the only forms in which the present invention may be constructed or utilized. The described embodiments, in conjunction with the described embodiments, set forth the functions and sequence of steps for constructing and operating the invention. It is to be understood, however, that the same or equivalent functions and sequences may be accomplished by different embodiments that are also intended to be encompassed within the spirit and scope of the invention.

To improve the ability to meter precise doses of a drug in vapor form for inhalation from a vapor delivery device, the vapor delivery device requires a power control system capable of controlling the heat and duration of application to the drug in liquid form, or a fluid delivery system capable of precise, consistent, and repeatable release of precise volumes of the drug. These two methods: (a) controlling the amount of heat applied to the liquid, and (b) controlling the volume of liquid to be vaporized, can be used alone or in combination to improve the accuracy of the "dosing" of the drug provided by the vaporizer. As used in the claims, the term "drug" refers to a medicament, drug, oral medication, patent, drug, and the like for healing, treating, modifying, improving, restoring, alleviating, and/or curing a particular symptom, disease, or mental or physical condition, which includes an active ingredient or a combination of an active ingredient and a non-active ingredient injected into an expedient or dissolved in some other carrier.

The amount of heat applied and the duration are related to the amount of power supplied to the vapor delivery device. Therefore, in order to improve the functionality of current vapor delivery devices, the current devices must be implemented with a power control system that includes a means for providing the precise amount of power generated by the power source to heat the heating element to the minimum required temperature that enables the predetermined volume of liquid to fully evaporate. The minimum temperature required to completely evaporate the predetermined volume can be calculated based on the properties of the drug, particularly the expediency method or carrier. By knowing the minimum temperature required to vaporize a predetermined volume of drug, energy resources can be conserved by not using more energy than necessary, which is one of the problems with existing devices.

The means for providing the precise amount of power generated by the power source to heat the heating element to the minimum required temperature required to enable complete evaporation of the predetermined volume of liquid comprises a control circuit or integrated circuit 82 having a processor 500 that controls the power sent to the heating element 152 to ensure that only the necessary amount of power is provided to evaporate the particular volume released. Since the amount of power supplied to the heating element 152 is related to the resistance across the heating element, the processor 500 can be programmed to monitor the resistance value of the heating element 152 to indirectly know the resistance of the heating element 152 as a representative of the amount of power supplied to the heating element 152. Knowing the resistance value, the processor 500 can manage the amount of power supplied to the heating element 152. Measuring the resistance at the heating element has several advantages. First, power can be accurately measured and maintained for accurate measurement and maintenance of power. Second, the resulting voltage can be measured from the circuit, rather than from the battery, which can extend battery life. Third, it ensures that evaporation remains constant, thereby enabling dose measurement regardless of the life cycle of the battery and degradation of the heating element.

In some embodiments, the means for providing the precise amount of power may also include a boost converter, which is a switching DC/DC converter, and ultracapacitors 368a, 368 b. The boost converter uses a charge converter that functions with an H-bridge and an inductor/capacitor system. By using a boost converter, the charging current can be limited to protect the battery and allow the super capacitor to produce a larger discharging current of shorter duration. For example only, it may take 3 to 5 seconds to charge, but only 0.5 seconds to discharge. Thus, the battery may only observe a load of 100-200mA, but the capacitor may observe a load of 1A or more. By utilizing such a system, an alkaline battery 364 can be used, thereby improving the safety of the device.

The supercapacitors ("supercaps") 368a, 368b are electrochemical capacitors having a relatively high energy density. The energy density is typically hundreds of times greater than that of conventional electrolytic capacitors. The supercapacitors 368a, 368b can store two orders of magnitude higher than the storage capacitance of standard electrolytic capacitors.

The circuitry of the present invention charges the supercapacitors 368a, 368b from a bank of alkaline batteries 364 using a DC/DC boost converter. A number of parameters must be considered when charging the supercapacitors 368a, 368 b. For illustration purposes, a 300 farad capacitor bank to be charged to 6V DC may be used, with a 6V power supply (4-1.5V AA battery) capable of generating 1.2AMAX current. Note that a resistor may be used in this circuit to limit the current to a maximum amperage, e.g., 1A, etc., as an additional control for the heating circuit.

To define how the charging circuitry of the present invention works, the charging resistor value =6V/1A =6 ohms using the ohm's law equation. This is determined using ohm's law: r = E/I, where R is resistance in ohms, E is energy in volts, and I is current in amps.

To determine the amount of power required to charge the capacitor bank, a "power" is utilized, which is electrically described as "wattage". This power equation is described as:

resistor power =6V x1A =6W (power = voltage x current)

Therefore, to charge a 6V capacitor bank with a 6V power supply (4 AA/AAA battery) at 1A, a 6 ohm resistor with a wattage rating of 6W or higher is required. In some designs, fewer batteries, such as one, two, or three batteries, may be used to supply sufficient power.

Using this approach, the present invention solves the standard problem in the battery life problem that current electronic cigarettes (e-cigarettes) have. In addition, this method provides the ability to maintain sufficient power to vaporize liquid using standard alkaline chemical batteries that are not available with current e-cigarette devices.

Fig. 36 is a block diagram illustrating the process. There is an energy source or power supply 600 that supplies input power. This power supply may be one of several types, but is generally suitable for both types. Type 1 may be a low power supply that does not operate directly at higher currents. This type of power supply requires additional regulation to support the full functionality, thus requiring the power conversion module 602 as well as the power storage module 608. Type 2 may be a high current source that allows direct drive of the evaporation element.

State or control logic 604, which may be dedicated logic or a processor, provides control, measurement, and drive functions. One embodiment may use a Texas instruments MSP430processor (Texas Instrument MSP430 processor), but it may be any processor or ASIC-like device. GPIO and a/D functions may also be used to allow measurement of current (direct drive) or voltage to the power storage (super capacitor). When all conditions are met, control logic 604 activates discharge switch 610 to heat vaporization element 612.

The ability to accurately measure and meter the power energizing the evaporation element 612 enables evaporation to be performedThe vapor phase transition and the dosage are precisely metered. In a direct drive system, the current and time of the drive is used to calculate and meter the energy used to heat the evaporation element 612. In a stored energy system, formula 1/2CV²Used to calculate the energy in the system and the terminal voltage required to meter the energy used to heat the evaporation element 612, where C is capacitance and V is voltage.

An alternative to controlling the amount of power when the power source begins to deplete is to control the charging time of the heating element. The processor 500 may be configured to monitor the resistance and adjust the time that the heating element remains on to completely vaporize a given volume of the drug.

In some embodiments, the flow switch 614 may be used to signal the initiation of the evaporation phase request. When implemented in an evaporation device, the device may have a fluid delivery system (discussed below). The fluid delivery system places a desired amount of fluid on the vaporization element 612 prior to activation of the flow switch 614.

In some embodiments, the fluid release actuator 616 may be used to "wake up" the processor 604 and charge 606 the supercapacitor 608 (in a stored energy system). In a direct drive system, a fluid release actuator may be used to "wake up" processor 604 from an ultra low power sleep mode. The fluid release actuator 616 may be a mechanical device for activating the system, such as a rotary switch, button, knob, lever, and the like.

In some embodiments, diodes 618, 620 may be used to indicate the status of the system operation to the operator. For example, one diode may be an LED618 to signal when the evaporation element 612 is driven. Another LED620 may be used to flash a particular pattern to indicate a system condition, such as power up, low battery, depleted fluid status, or other system specific condition status (i.e., maximum dose per unit time, etc.). In other embodiments, a display, such as an LCD screen, may be used to display system status or other information, such as the type of substance or drug contained in the delivery device, the amount and/or dose remaining, battery charge level, user ID in the event of device loss, etc. Buttons or similar devices may be used for actuation and scrolling through the display.

In type 1 configurations (low current, alkaline batteries, etc.), the charging current is limited to maintain the life cycle of the battery. In many batteries, if a large amount of current is generated, the battery life or state of charge will be significantly shortened. Thus, using a lower current generated from the battery and power storage module 608 can allow for high current situations without unduly draining the battery.

In a type 2 configuration, power storage 608 may be used to extend the life of the battery (lithium polymer, lithium ion) if necessary. The power storage 608 also makes it easier to very accurately meter the precise amount of energy entering the vaporization element 612 with a simple voltage measurement. Accurate metering of the precise amount of energy into the evaporation element can be accomplished by voltage and current measurements, but it is difficult to accurately measure current in this way as compared to measuring voltage. It is therefore advantageous to use a simpler process of measuring only the voltage.

Another feature to conserve power is that the control logic 604 is shared with the power conversion 602, i.e., the power state of the system (when powered on). This power saving feature of the power state can be achieved by either an ultra low power mode of the switching/cpu or a power off/latching function. This serves to extend the operational life of the device after first use.

The energy required to fully evaporate the predetermined volume of liquid varies with the amount of power and the duration of time that the power is present. Accordingly, power control system 306 may also include means for controlling the precise duration to provide the precise power required to completely vaporize a predetermined volume of liquid at a desired temperature. The means for controlling the precise duration of supplied power may include "one shot" control circuitry 170, 172 or 174, which may be integrated with the circuitry for controlling the amount of power described above. Examples of "one shot" circuits 170, 172, or 174 are shown in fig. 15-17 and will be described in detail below. The "one shot" circuit can be used to limit the current delivery time interval regardless of how long the user presses the lever down. Power control system 306 is completely "off" between each use; the battery is not discharged during the idle period. Therefore, the life of the battery is extended.

In some embodiments, the integrated circuit may be configured to power up the power supply a predetermined number of times. This number should be low enough so that each start-up produces the same amount of power. In some embodiments, the integrated circuit may be configured to monitor battery life and not activate power when a predetermined amount of battery life is detected.

Such a power control system 306 may be implemented in existing vapor delivery devices. For example, the control system 306 may be installed into the handle of current vapor delivery devices to be implemented with existing heating systems to improve the energy efficiency and accuracy of dosing of current devices.

Additionally, or in addition, a means for consistently metering the precise volume of liquid to be vaporized may be used to produce alternative or additional accuracy, while or in addition to controlling the amount and duration of power to significantly improve the efficiency and effectiveness of the vaporization apparatus in metering precise doses. Thus, a highly efficient drug delivery device may comprise: power control system 34 utilizing multiple embodiments of the circuitry described above to control the efficient and effective use of power; and/or fluid delivery system 30, 302, or 402 as a means to consistently meter a precise volume of liquid from a fluid reservoir to precisely control the volume of discharged liquid for vaporization. Different combinations of these systems may be used to achieve the desired level of accuracy. An aerosolization or vaporization system 32 may also be required to vaporize the drug. In this application, nebulization and evaporation are interchangeably applicable to indicate a form that can be inhaled and absorbed by the lungs.

The exact volume of liquid that can be completely evaporated at a given temperature and duration of exposure can be calculated. Since the temperature of the wire and the duration of time the wire is energized may be fixed, the precise volume that needs to be released from the fluid delivery system may be predetermined. Alternatively, in some embodiments, the precise volume may vary depending on the temperature of the wire and the time the wire is energized at that temperature.

The embodiments of the power control system described above provide an advantageous way for more accurate metering of a specific dose of a drug. Controlling the volume of drug released also improves the accuracy of metering. An example of a device for controlling the volume of drug reaching a heating element for vaporization is described below. These devices may be used alone or in conjunction with a power control system to further improve the accuracy of the metered dose of the medicament.

In one embodiment, as shown in FIGS. 1 and 2, the drug delivery device 20 has an elongated housing 22 with a mouthpiece 24 and a lever 28 adjacent the back or top end of the housing. The mouthpiece opening 26 extends into the mouthpiece 24. With further reference to fig. 3-5, one embodiment of the apparatus 20 comprises: a fluid or liquid delivery system 30 as a means to consistently meter precise volumes of liquid to precisely control the volume of released liquid for evaporation; and an evaporation system 32 and an electrical power control system 34. The electrical power control system 34 may include a battery 44 located within the battery compartment 42 of the housing 22, and wherein the battery is electrically connected to the flexible circuit board 82 through the spring 46 and the contacts 48. As shown in fig. 5, the housing may have a clamshell design on the left and right sides. The lever 28 may be attached to the housing 22 at a pivot 58.

As shown in fig. 4, a means for consistently metering the precise volume of liquid from the fluid reservoir to precisely control the volume of liquid discharged for evaporation may be achieved by the liquid delivery system 30, which in the example shown includes a resilient or curved-walled liquid chamber or reservoir 64 connected by a tube 66 to a lever valve 70. The reservoir 64 may be a thin-walled flexible bladder made of polyethylene film. The reservoir 64 is placed between two rigid surfaces with the plate 62 on one side and the inner wall of the housing 22 on the other side. A spring 60 within the housing 22 presses against a plate 62, which in turn presses against a reservoir 64. This pressurizes the liquid in the reservoir.

The tube 66 extends from the reservoir 64 to a lever valve 70, which may include a valve post 74, a valve spring 72, and a valve gasket 76. In this design, the valve portion 80 of the tube 66 extends through the opening of the valve post 74, as shown in FIG. 6. The valve spring 72 urges the valve gasket 76 against the valve portion 80 of the tube, pinching the tube closed.

Referring to fig. 4-6, one embodiment of the vaporization system 32 includes a heater 150 electrically connected to the electrical power control system 34. The vaporization system 32 is also connected to the liquid delivery system 30 and receives liquid from the liquid delivery system 30. The heater 150 may be a resistance heater formed from an open coil 152 of nichrome wire or the like. In this design, current is supplied to the coil 152 through a connector 156 located on the flexible circuit board 82 or connected to the flexible circuit board 82, which in turn is connected to the battery 44. Fig. 14 shows a connector 156 for supplying electrical power to the heating element.

An outlet section 154 of the tube 66 extending outside the joystick valve 70 toward the mouthpiece or back end of the device is inserted into the front end of the coil 152. Referring now to fig. 14, solid wire inserts 159 may be inserted into the ends of the coil 152 and the outlet section 154 to provide internal support so that they do not deform or collapse when pressed down into the connector 156. With each actuation of the device 20, an outlet section 154 at the forward end of the coil heater 152 provides liquid into the coil bore.

The tube 66 is connected to the reservoir 64 by a liquid-tight connection, so that liquid can only flow out of the reservoir through the tube 66. Tube 66 may be of a resiliently flexible material such that its lumen may be substantially completely flat when compressed and then substantially completely return to its original shape when released. The lever section 67 of the tube 66 is located below the lever 28 and a fixed rigid surface inside the housing, which may optionally be part of a circuit board 82 on which the power management circuitry is located. Locating features 112 may be provided in the circuit board 82, on the circuit board 82, or through the circuit board 82 to ensure that the desired positioning is maintained. The lever 28 is held by the lever pivot 116 and can pivot through a controlled range of motion.

In use, the mouthpiece 24 is placed in the mouth and the user presses or squeezes the lever 28. During manufacture, the tube 66 is pre-filled or filled with a liquid. Referring to fig. 4, as the lever 28 pivots downward about the pivot 58, the pincers 86 pinch the lever section 67 of the tube 66 against the inner surface of the housing 20, adjacent the pivot 58, and the reservoir 64. This temporarily closes tube 66 at pincer 86. As the lever 28 continues to pivot downward (or inward toward the centerline of the device), the ramp surface 88 of the lever 28 gradually compresses the lever section 67 of the tube 66 between the forceps 86 and the lever valve 70. This creates a squeezing type of movement to pump the liquid toward the stem valve 70 using a peristaltic action. As the lever 28 continues to pivot inwardly, a post on the lever presses the valve gasket 76 downwardly against the force of the valve spring 72. This temporarily opens the lever valve 70 by opening the valve portion 80 of the tube 66. As the valve portion 80 of the tube opens, and as the liquid in the tube is pumped through the ramp surface 88, a large amount of liquid flows through the valve portion 80 and the outlet section 154 and into the coil 152.

The constant positive pressure exerted by the spring 60 on the reservoir 64 pressurizes the liquid in the tube 66. However, since the tube 66 is pinched closed by the pliers 86, no liquid flows from the reservoir when the lever is depressed and the lever valve is open. Instead, the liquid already present in the tube 66 between the pincers 86 and the lever valve 70 provides a measured amount of liquid that is evenly delivered into the coil.

Downward movement of the lever 28 also causes a switch 158 attached to the circuit board 82 or located on the circuit board 82 to close. Current then flows from the battery 44 or other power source into the coil 152. The heating of the coil causes the liquid to evaporate. In operation, the current supplied to the coil and the temperature of the coil may be regulated by the circuit board, depending on the liquid used, the dosage required, and other factors. The switch 158 may be in the closed position only when the lever 28 is fully depressed. This avoids accidental heating of the coil. This also delays heating of the coil until a large amount of liquid is moved into the coil by the pivoting movement of the lever, thereby contributing to the life of the battery. For example, a "one shot" control circuit 170 as shown in fig. 15 and described below may be used to limit the current delivery time interval regardless of how long the user holds the lever down. The power supply is completely "off" between each use. The battery is not discharged during the idle period. Therefore, the life of the battery is extended.

As will be apparent from the present description, with each actuation of the device 20, the liquid delivery system 30 using a linear peristaltic pumping action delivers a consistent, fixed, repeatable, large volume of liquid into the vaporization system 32. The liquid delivery system 30 further seals the reservoir 64 between each actuation by the forceps 86, maintains the contents of the reservoir in a pressurized state, and controls the electrical power delivered to the vaporization system 32. The liquid delivery system is designed so that air is not introduced into the system as the liquid is used.

The diameter and length of the coil 152 forms a cylindrical volume within the inner diameter of the coil sufficient to capture a single delivered dose of liquid from the liquid delivery system. Adjacent loops of the coil 152 may also be positioned such that liquid surface tension holds the liquid within the coil bore. This allows the device 20 to be used in any orientation since gravity is not required to hold the released liquid dose in place.

The use of open coils provides the further advantage that vapour can be generated and escape anywhere along the length of the coil without adversely affecting the equilibrium evaporation of the bulk liquid within the coil. The coil also provides a large surface area for heat transfer and minimizes energy loss due to heating of the auxiliary components.

After application of the electrical power, the liquid in the coils evaporates and passes through the gaps between the coils. The coil may be sized and shaped and positioned in the housing such that when a user inhales on the mouthpiece, the generated vapor may be entrained in the air stream inhaled by the device 20. By "inhaling" is meant herein at least inhaling the vapor into the mouth.

Fig. 7-13 illustrate a second apparatus embodiment 100 that may be similar to apparatus 20, but with the following differences. In the device 100, the means for consistently metering the precise volume of liquid from the fluid reservoir to precisely control the volume of discharged liquid for evaporation includes a foam pad 106 that is compressed and interposed between the reservoir 64 and one of the rigid walls of the housing. The force exerted on the reservoir 64 by the foam attempting to return to its relaxed state exerts a compressive force on the reservoir, thereby maintaining the liquid within the reservoir under pressure. The foam pad 106 may be used in place of the spring 60 shown in fig. 4. The reservoir may alternatively be pressurized using a syringe having a spring-biased plunger. By any of these designs, the reservoir may alternatively be designed as a replaceable cartridge.

As shown in FIG. 8, in the device 100, a lever valve 118 (instead of the pincers 86 in the device 20) is provided to compress the forward end of the tube 66 to prevent liquid from flowing out of the pressurized reservoir between each use. The lever valve 118 may be in the form of a stamped sheet metal that is soldered to the rigid circuit board 114 containing the same or similar circuitry as described above for the power control system 34.

Fig. 10-13 illustrate other features that may be used with a means for consistently metering the precise volume of liquid from a fluid reservoir to precisely control the volume of discharged liquid for evaporation, and in particular, the pumping action of the liquid delivery system in the device 100. When a dose of steam is required, the user places the mouthpiece in the mouth and inhales while pressing the button 109 on the lever 110, causing the lever to rotate downward (counterclockwise). As the lever 110 is initially rotated as shown in fig. 10, the lever clamping protrusion 132 clamps or clamps the tube 66 closed at the clamping point 140, thereby closing the pressurized liquid reservoir. Continued rotation of the lever 110 causes the lever 110 to bend at a bend point 124 having a reduced thickness, as shown in FIG. 11. This allows the lever to over-rotate without crushing the tube 66 while it remains closed at the pinch point 140.

Further rotation of the lever 110 then compresses the cavity in the pump section 68 of the tube 66. This may pump liquid from pump section 68 toward joystick valve 118. This movement also moves a protrusion on the lever that pushes the valve flange 120 downward, deflecting and opening the lever valve 118 and allowing a large volume of pressurized liquid to move through the tube and into the evaporation system 32. The dashed lines in fig. 12 show the lever valve 118, the lever valve 118 deflecting downward and away from the bottom surface of the circuit board 114 to open the valve. Finally, at the end of the lever stroke, the lever switch projection contacts the switch 158, thereby turning the power delivery system on.

When the operating lever 110 is released, it pivots back to its original position. With the lever returned, the lever valve 118 is first reset, sealing the back end of the pump section 68 of the tube 66 and preventing air from being drawn back into the pump section. As the lever 110 continues to rotate clockwise, the pump section 68 decompresses, creating negative pressure within the lumen. Finally, at pinch point 140, tube 66 reopens, allowing pressurized liquid from the reservoir to enter the now liquid-filled pump section 68 to provide the next dose.

The volume of liquid delivered by each stroke can be controlled by selecting the tube diameter and length of the desired pump section 68. Maintaining a positive pressure on the liquid reservoir ensures that the system is always filled with liquid and that no "short triggers" caused by air bubbles in the tube occur. In addition, sealing the vaporizer system with a valve, such as valve 70 or 118, that is actuated only at the time of delivery, and the dispensing of positive pressure prevents inadvertent leakage of liquid regardless of the orientation of the device during storage or use, thereby providing a means for consistently metering an accurate volume of liquid from the fluid reservoir to accurately control the volume of discharged liquid for vaporization.

FIG. 15 is a schematic diagram of a "one shot" circuit 170 for a power control system that delivers a fixed interval of current to the heater 150 regardless of how long the user depresses the lever. In fig. 15, CD4047 is a CMOS low power monostable/astable multivibrator available, for example, from texas instruments. Ul is a generic CD4047, which is operated with a 12V battery voltage with very low quiescent current drain. When button SW1 is pressed, Ul is toggled, Q (pin 10) goes high, and C1 is quickly charged to near supply voltage by the FET in Ul. At the same time, resistor Rl switches to a logic "0" state and immediately begins to discharge capacitor C1 with a time constant of 1/RC.

A wide range of pulse durations may be selected. Using a typical nichrome coil, a pulse duration in the range of about 0.2 to 2 seconds is sufficient to completely evaporate the bulk liquid. When the voltage on pin 3 reaches the threshold of logic "0" (1/3 supply voltage), the logic level switch and thus Q (pin 10) return to a logic low level. Q2 is an emitter follower that provides current amplification so that Ql is fully saturated during the required current pulse. Dl and R4 provide a visual indication of heater current. R2 is a "pull down" resistor to SW1, and C2 prevents the induced noise from falsely triggering the circuit. Other choices of IC may also be used, for example toshiba TC7WH123, depending on battery voltage, package size, and cost.

The battery voltage gradually decreases over the life of the device. For many applications, the circuit depicted in FIG. 15 provides the necessary control. However, more accurate metering of the drug may be achieved by: the duration of the current pulse is increased as the current decreases during the discharge life of the battery. In the circuit 172 shown in fig. 16, an additional operational amplifier IC is used as a current source for the voltage control of the power control system. The input voltage is sampled from pin 10 of Ul. A constant current is generated in Q3 and is used to discharge timing capacitor C1 at a constant rate. After the voltage across C1 reaches the logic threshold, CD4047 trips and the output pulse width is complete. As the battery voltage decreases, the constant current generated in Q3 decreases, causing the time to discharge C1 to increase. This extends the output pulse to maintain a relatively constant heater power per suction cycle as the battery voltage decreases over the life of the device. Various current settings and sense resistor values may be adjusted to provide optimum performance. Other circuits may be employed to provide the same functionality, such as a voltage to frequency converter.

Fig. 17 shows another circuit 174 for a power control system, where a voltage regulator U2 is inserted between the output transistor Ql and the heater filament. This keeps the filament voltage constant throughout the battery life. The regulated voltage may be selected to optimize heater operation near the end of life. A low dropout regulator is needed to maximize life before regulation is no longer maintained. A simple linear regulator is shown, but a high efficiency switching regulator may also be employed to improve efficiency. The pulse duration is maintained as described above or an equivalent "one shot" circuit and heater current is held constant by the voltage regulator.

In another alternative design, the electrical power control system 34 may be configured to provide consistent power by timing the power to provide the minimum energy required to vaporize the liquid. Power control system 34 may also be programmed to achieve this. For example, the electrical power control system 34 may be programmed to reduce the electrical power of the power source to the voltage required to vaporize the liquid, thereby extending its useful life. Here, the power supply may comprise a capacitor which establishes, maintains and supplies the amount of electricity necessary for the evaporation of the liquid to be evaporated, thereby again extending the service life of the power supply. In some embodiments, a super capacitor may be employed as described above to further enhance the functionality of the power supply.

In a further alternative design shown in fig. 18, the liquid to be atomized is delivered by capillary action into a small diameter tube 180, as opposed to providing the liquid into the heating coil by pressure, where it is stabilized for evaporation due to surface tension. The tube 180 may be glass, polyaniline, or metal, e.g., stainless steel. A heating element such as nichrome wire may be wrapped around the tube, wrapped into the tube, or inserted into a V-shaped tube to heat the entire volume of liquid at the same time.

Fig. 19-22 show an alternative vaporizing device 200 having a housing formed by a base 202 including a mouthpiece 206 and a cover 204 attached to the base 202. As shown in fig. 21, a pivot arm 209 on the button 208 is pivotally attached to a pivot post 226 on the bridge 224 to provide another means of metering in unison a precise volume of liquid from a fluid reservoir 234 to precisely control the volume of liquid discharged for evaporation. When tube 236 is compressed, radius 244 of forceps 238 may bend. The bridge 224 has pins for securely attaching it to the base 202. The positive electrode of each cell 44 is in contact with the center contact 212 by a spring 46. A positive conductor strip (positive conductor strip) 214 connects the center contact to a printed circuit board 216.

Referring to fig. 22, a die 220 extends from the printed circuit board 216 (containing the same or similar circuitry as described above for the power control system 34) up to the evaporation coil 222 and optionally on the riser 240. The die may be a strip or sheet of ceramic tape 220 that acts as a die and heat spreader. The wick 220 is located between a heating element such as an evaporation coil 222 and the outlet of the tube 236. The wick 220 may rest on top of the heating element or may be positioned adjacent to the heating element, and the tube outlet may also be located on the heating element and on top of the wick 220 (with the button 208 on top when the device 200 is in an upright position).

Brass posts 218 or similar contacts are attached to the printed circuit board 216 and to opposite ends of the coil 222. Button 208 has a tweezer arm 209 positioned to pinch and close off flow in a tube 236 that connects the liquid reservoir to an outlet location on, adjacent, or covering die 220, die 220. Tube 236 is held in place by molding in tube clamp 240 on bridge 224. An arm 233 on the normally closed pinch valve 232 extends upwardly through an opening in the bridge 224. A valve spring 230 surrounding the post 228 holds a valve 232 in a normally closed position. The bottom surface of the valve 232 may be used as a switch on the printed circuit board 216 or to actuate a separate switch on the printed circuit board 216 to turn on the current to the coil 222 when the button 208 is pressed.

In use, the evaporation device 200 operates according to the same principles as described above, with the following additions. Slots 210 may be provided in the housing to accommodate insulated contacts. The insulated tabs are installed at the production stage and prevent electrical contact between the center contact 212 and the cell. Thus, the device is not accidentally opened during transport and storage. Thus better maintaining battery life. Before the first operation of the vaporizing device 200, the user pulls the tab out of the slot 210. As shown in fig. 19 and 20, the mouthpiece is circular. The dimension LL between the coil 222 and the mouthpiece tip in fig. 20 can be minimized to 15, 10 or 5 mm. The liquid reservoir may have a volume in excess of 0.8 or 1.0ml to allow the foam to compress to pressurize the pump. In device 200, liquid supplied from the reservoir through tube 236 is not delivered to coil 222. Instead, the liquid is delivered onto the wick 220. The heating coil 222 is adjacent to and heats the die 220, which then vaporizes substantially all of the liquid located on or in the die.

In each of the vaporization devices described above, for example, the open coil heater 152 or 222 of nichrome wire may be encased in a porous ceramic material such that the vapor generated upon atomization of the fluid must pass through the ceramic material for absorption or inhalation. The ceramic material may be manufactured by a technique that controls the size of the pores through which the vapor passes. This may help to adjust the size of the vapour molecules or droplets generated for inhalation. By controlling the amount of electrical power to the coil heater and the duration of the power, the heater continues to vaporize the fluid at the heater until the vapor droplets or particles are small enough to pass through the ceramic material, thereby effectively utilizing all of the fluid delivered to the coil and controlling the dosage in addition to adjusting the molecular size. By adjusting the size of the vapor molecules generated, the vaporization device can be used with greater precision and can be used with fluids and drugs that require careful control of the dose particle size. In some cases, smaller molecules may be more advantageous because they may be inhaled deeper into the lungs, better providing a more efficient delivery mechanism.

The coil heater may optionally be encased in a heat resistant fabric-like material, e.g. KevlarAnd therefore the steam must pass through the fabric for absorption. The fabric can be made according to the desired mesh opening size to adjust the size of the vapor particles and/or molecules delivered by the evaporator. By regulating the amount and power of electric power to the heaterThe duration is controlled and the heater continues to evaporate the fluid delivered to the heater until the vapor particles are small enough to pass through the web of fabric. The inclusion of the fluid in the fabric with the heater until the particles are small enough to pass through the fabric can help to effectively atomize and deliver all of the delivered fluid to the heater with little or no waste, which in turn controls the dosage.

Although switch 158 is described above as a mechanical contact switch, other forms of switches may alternatively be used, including switches that optically or electrically detect movement of a component or switches that detect the presence or absence of liquid in heater 150. Further, while the lever and pinch valve are shown as pinch type valves, other forms of mechanically or electrically operated valves may be used. Similarly, the peristaltic pumping action created by the pivotal movement of the lever may optionally be replaced with an alternative form of pumping or fluid movement. Various types of equivalent heating elements may also be used in place of the coil. For example, a solid heating element may be used. The heating element may also be replaced by an alternative evaporation element, for example an electro-hydrodynamic or piezoelectric device that converts a liquid to a vapor without heating.

In another embodiment, the delivery device 300 uses the plunger-type liquid delivery system 302 as another means to consistently meter a precise volume of liquid from a fluid reservoir to precisely control the volume of liquid discharged for evaporation. As shown in fig. 23, the delivery device 300 incorporates a new liquid delivery system 302, but utilizes the same or similar atomization or vaporization system 32 and power control system 34 described above, all contained in a housing 308, which is preferably cylindrical in shape to simulate a cigarette or cigar.

The fluid delivery system 302 has a fluid reservoir 310 to contain the drug and a pressure generator, e.g., a piston 312, that indexes forward in the fluid reservoir 310 in a consistent, fixed, repeatable amount each time a fluid release actuator, such as a button 314, is depressed or activated. Preferably, the fluid reservoir 310 is cylindrical and, more preferably, shaped like a syringe. The delivery device 300 is completely sealed between applications such that the drug cannot evaporate during storage or between actuation cycles.

The fluid reservoir 310 has a proximal end 316 and a distal end 318. The proximal end 316 is configured to receive the piston 312, which forms a hydraulic seal against the wall of the reservoir 310 such that the drug cannot leak past the piston 312. The piston 312 may have a hollow core 313. A plunger 320 is provided to couple with the piston 312 to drive the piston 312 forward in a controlled and step-like manner. The plunger 320 includes a shaft 322 having a head 324 at one end. In a preferred embodiment, the head 324 is flanged. The head 324 is configured to engage with a mating geometry inside the piston 312, securing the piston 312 to the plunger 320. The shaft 322 of the plunger is provided with male screw threads 326, preferably male screw threads 326, over its entire length.

A drive nut 328 is disposed at the proximal end 316 of the reservoir 310. Various features of the housing 308 and the reservoir 310 constrain the position of the drive nut 328 so that it is free to move rotationally simultaneously with the axis a of the plunger 320, but prevent translation in any other direction. The drive nut 328 has female screw threads 330 that mate with the plunger 320 and is threaded onto the plunger 320. The drive nut 328 is further configured with ratchet teeth 332 that interact with a pawl 334 on the button 314, described later, such that the drive nut 328 will rotate in a single direction during operation.

A cap 336 is disposed at the distal end 318 of the reservoir 310. The cap 336 may be an elastomeric component having an outlet 338 that includes a self-collapsing slit/hole. Preferably, the cap 336 is made of silicone. The outlet 338 is responsive to the pressure created by the drug within the reservoir 310, so that when the drug is at a higher pressure than the ambient pressure outside the reservoir 310, the outlet 338 will open 338A, allowing the drug to exit the reservoir 310. After sufficient drug leaves the reservoir 310 to equilibrate with ambient pressure, the outlet 338 will automatically collapse, thereby blocking the remaining contents within the reservoir 310 from the outside environment, thus preventing loss of drug by evaporation. Thus, the measured dose is determined by appropriate calibration of the pressure required to properly form and maintain the drug droplet at the outlet 338 until evaporation begins. The nature of the seal is such that changes in pressure outside the device do not cause the reservoir to become "unsealed" and changes in external pressure are not "unsealed" because they are sufficiently concentrated or strong. And the natural resiliency of the reservoir will cause the seal to "reseal" regardless of changes in external pressure.

Based on the surface tension of the liquid drug, the volume of drug released from the outlet 338 should be small enough so that the drug forms droplets at the outlet 338 that adhere to the outlet 338 without falling or dripping from the cap 336. The distance from the outlet 338 to the coil 152 should also be small enough so that a droplet of liquid formed at the outlet can bridge the gap between the outlet 338 and the coil 152, thereby allowing the droplet to be transported into the coil 152 or the wick 360 within the coil 152. This configuration allows the vapor delivery device 300 to be used in any orientation; and thus have more uses than current devices.

As shown in fig. 30, the function of the button 314 is to provide controlled rotational indexing of the drive nut 328. The button 314 includes a control surface 340 protruding through the upper housing for a user to actuate the button 314. In its neutral (home) position, the button 314 typically protrudes slightly from the housing 308. The button 314 is constrained such that, when pressed, it can translate in a direction perpendicular to the control surface 340. The button 314 is provided with two spring elements 341a, 341b which bias the button back to its neutral position in the absence of pressure on the control surface 340. The spring elements 341a, 341b are designed to deform under pressure on the load surface and return to their original shape after the pressure is released. The range of button movement is limited by a stop 342 having an upper surface 343a and a lower surface 343 b. The stop surfaces 343a, 343b engage the opposing surfaces of the lower and upper housings at the extremes of button travel, providing a fixed range of displacement for the button 314 when the button 314 is depressed/released. The button 314 is further configured with a pawl 334 to engage ratchet teeth 332 on the drive nut 328. When the button 314 is depressed, the pawl 334 engages the ratchet teeth 332, causing the drive nut 328 to rotate. When released, the ramped surface 344 of the pawl 334 and the opposing surface 346 of the ratchet 332 oppose each other, thereby deflecting the pawl 334 at one web such that the pawl 334 slides past the adjacent ratchet tooth and returns the button 314 to its neutral position. In this manner, the ratchet 332 allows the drive nut 328 to rotate in a single direction.

In some embodiments, button 314 enables power delivery to heating system 304 to be initiated in synchronization with the delivery of a quantity of medication to vaporization system 32. As shown in fig. 31A and 31B, contact pins 348 are provided across the button spring elements 341A, 341B. During actuation of the button 314, the bias of the spring elements 341a, 341B causes the contact pins 348 to be lower than the contacts 350a, 350B, thereby closing the circuit through the contacts 350a, 350B, as shown in fig. 31B. This closing is used to initialize the power cycle to the vaporization system 32, as described below. In some embodiments, the contacts 350a, 350b may be located directly below the spring elements 341a, 341 b. The underside of the spring elements 341a, 341b may have individual contact pins 348 to connect with the contacts 350a, 350b to close the circuit. In some embodiments, a single contact pin 348 and a single contact 350a may be used.

The pitch of the threads 326 is selected to allow for the aperture 352 of the reservoir 310, as well as a controlled angular degree of the drive nut 328 to transfer the desired bolus of medicament from the reservoir 310 with each indexing of the drive nut 328. All rotational movement of the drive nut 328 is translated into linear movement on the plunger 320 to provide consistent, fixed and repeatable doses of medicament. To ensure that the plunger 320 does not rotate with the rotary drive nut 328, the plunger 320 is further provided with a downwardly extending length of a groove 354, the groove 354 receiving an anti-rotation tang 356 protruding from a lower portion of the housing 308, as shown in fig. 32.

An atomization or vaporization system 32 similar to that described above includes a close coil heater element 152 located adjacent the fluid delivery system outlet 338. In a preferred embodiment, the coil 152 is a nichrome wire. In some embodiments, nichrome coil 152 may be wrapped around high temperature fiber wicking element 360 to dispense the received dose of drug throughout coil 152.

The power control system 34 includes a circuit board 362 (containing the same or similar circuitry as described above) and an associated battery 364 which delivers a fixed and precise amount of power to the nichrome wire 152 at each actuation, the amount of power delivered being that amount necessary to aerosolize or vaporize a precise volume of the delivered large quantity of medication. To achieve optimal system efficiency, it is desirable to maximize the energy density of the heater. The coils of the heater should ideally be spaced as closely together as possible. In addition, it is desirable to distribute the dose of medicament to be vaporized as evenly as possible over the heater element. To this end, the heater coil 152 is wrapped around a die 360 comprising a high temperature resistant material that forces the drug to be evenly distributed throughout the die 360. The coil 152 is connected to the power control system 34 by a crimp connector 366. In a preferred embodiment, circuit board 362 contains a one-shot circuit (similar or identical to the circuitry described above) that delivers a fixed and precise amount of power to nichrome heater 152 upon each activation, the amount of power delivered being necessary to aerosolize or vaporize the delivered bolus medication.

In some embodiments, to further provide a means for delivering precise amounts of power to the vaporization system 32, the power control system may include one or more ultracapacitors 368a, 368b connected to a power source and circuitry. The use of ultracapacitors 368a, 368b prevents the amount of power received by vaporization system 32 from varying as battery 364 is gradually depleted. Specifically, the ultracapacitors 368a, 368b prevent the power delivered to the vaporization system 32 from dropping as the battery is depleted. Without the circuitry to precisely control power, the reduced battery power would result in a reduced temperature of the wire 152 for a given activation. In this case, incomplete evaporation of the drug may occur if the volume of the drug remains unchanged.

Fig. 33-35 illustrate another embodiment of a delivery device 400. Fig. 34 shows the delivery device 400 with the housing 408 removed. The delivery device 400 includes the same or similar vaporization system 32 and power control system 34 as described above, with another embodiment of a fluid delivery system 402 having means to meter a precise volume of liquid from a fluid reservoir in unison. The housing 408 of the delivery device 400 is also different from the housing of the delivery device 300. The housing 408 generally has an elongated box-like configuration. The housing 408 may also take other shapes, such as a cylindrical shape or any shape or size as desired for a particular application. The housing 408 has a top end 410 and a bottom end 412 opposite the top end 410. Top end 410 includes a cap 414.

A suction tube 416 protrudes from the top end 410. The aspirator tube 416 is operatively connected to the fluid delivery system 402. The medicament from the fluid delivery system 402 is vaporized by the vaporization system 32 and the vapor flows through the inhaler tube 416 and into the user's mouth. The cover 414 serves to protect the inhaler tube 416 when not in use. Fig. 33 shows the cover slid, however, the cover 414 may be flip-open, removable, slidable, etc. When the cap 414 is pushed back from the top, away from the top, off the top, or removed from the top, the inhaler tube 416 is released and rotates upward. The user may then initiate the inhalation process by means of the inhaler, which initiates the heating process by activating the flow sensor.

At the bottom end 412 of the housing 408 is a handle 418 to deliver a precise volume of drug from the fluid delivery system 402 to the vaporization system 32. Similar to the button 314 of the device 300, the handle 418 at the bottom 412 of the device 400 is used to repeatedly advance a plunger (not shown) through a syringe (not shown) in a step-wise fashion similar to that used to deliver a precise, fixed, and consistent volume of medication from the syringe and place it on the coil 152 of the vaporization system 32. Each rotation of the handle 418 advances a precisely metered amount of the medicament in a consistently repeatable volume.

As with the previous version, the device 400 utilizes a circuit board 420 (containing the same or similar circuitry for the power control system 34 as described above) and associated processor (not shown), supercapacitors 368a, 368b and other electronic components for delivering consistent, precise and sufficient amounts of power to the heating system to vaporize or atomize a predetermined volume of liquid. The circuit board 420 is positioned adjacent to the fluid delivery system 402 and the vaporization system 32 at the top end 410. The through hole 430 is provided to allow the inhaler tube 416 to pass through the circuit board 420, allowing the fluid reservoir 422 to be attached to this inhaler tube 416 and providing the inhaler tube 416 to a user.

A fluid delivery system 402 is mounted below the circuit board 420. This assembly provides a robust, tamper resistant chamber for retaining fluids. Subsequently, the fluid delivery system 402 is connected to a gear reduction assembly 424 that enables a linear syringe actuator to be advanced through the reservoir 422 in a consistent amount for each rotation of the handle 418.

Vaporization system 32 is placed in the path of the fluid being delivered by fluid delivery system 402 each time handle 418 is rotated. Vaporization system 32 includes heating coil 152. In some embodiments, the heating coil 152 may be wrapped around the wick 360, which helps retain the liquid after it is discharged from the fluid delivery system 402. After the fluid is propelled, the fluid wets the wick 360 placed in the heating coil assembly 152. After the wick 360 is wetted, the coil 152 is heated once the user begins to inhale (suck) on the inhaler tube 416. To activate the heating mechanism, a flow sensor (not shown) is placed in the suction path, which is the path between the inlet of the aspirator tube 416 and the outlet 417 of the aspirator tube 416.

As flow is detected when the user begins to inhale/suck on the inhaler tube 416, heating of the coil is initiated by applying a voltage to the coil 152. The power applied to the coil 152 is supplied through a supercapacitor assembly 368a, 368b, which is charged by the device battery 364.

To further improve the delivery and efficiency of the drugs delivered by the present invention, it is necessary to analyze the plume chemistry of the drugs delivered to the lungs. Depending on the size of the vapor product released by the vapor delivery device, the medicament may have utility in a number of places, thereby indicating the effectiveness and speed of the medicament on the user. For example, larger vapor products are more likely to be caught in the mouth, which may cause the drug to travel through the digestive tract. Smaller vapor products may be inhaled into the lungs, but may be trapped in the upper lung. Finer vapor products can reach the lower lung where the absorption of the drug is more efficient and rapid.

Again, to control the size of the vapor product, a permeable membrane of ceramic, fabric, or the like may be placed between the heating system and the mouthpiece. The heating element allows the medicament to evaporate, however, the vapor product is filtered through the permeable membrane before exiting through the mouthpiece to govern the size of the vapor product delivered to the user. The membrane should be made of a heat resistant material, such as ceramic or kevlarA material.

The consistent, reliable and accurate control of the dosage provided by the present invention allows its use far beyond mere use as a substitute for tobacco products. The device may be used to deliver food supplements, hypnotics, weight loss products, analgesics, and many other prescribed drugs and over-the-counter pharmaceutical products that require precise dosing. The invention may even be practiced in non-pharmaceutical fields, such as for dispensing liquid confections for consumption, breath fresheners, air fresheners, and any other application where evaporation of a consistent, reliable, and precise dosage of a liquid is desired.

While the system and apparatus have been described in connection with what is presently considered to be the most practical and effective embodiments, it is to be understood that the invention is not to be limited to the disclosed embodiments. All changes, enhancements, equivalents, combinations, and improvements which become apparent to those skilled in the art upon a reading of the specification and a study of the drawings are intended to be included within the true spirit and scope of the invention. The scope of the invention should, therefore, be accorded the broadest interpretation so as to encompass all such modifications and similar structures. It is therefore intended that the subject application include all such modifications, alterations and equivalents as fall within the true spirit and scope of the invention. Thus, a number of embodiments and methods have been illustrated and described. Various modifications and substitutions may be made thereto without departing from the spirit and scope of the invention. Accordingly, the invention is not to be restricted except in light of the above claims and their equivalents.

Industrial applicability

The invention has industrial applicability in the development, manufacture and use of a drug delivery system that delivers precise doses of a drug in vapor form to a user in a consistent, reliable and repeatable manner in an energy efficient manner. The delivery system includes a power control system, an evaporation system, and a fluid delivery system. The power control system utilizes a circuit system that allows the system to deliver just enough power to vaporize or aerosolize a known volume of drug. To avoid changes in current due to power depletion, the control system utilizes a super capacitor connected to the circuitry. The power supply and/or electrical resistance at the heating element can be monitored so that the system knows the amount of power that needs to be supplied to effect vaporization of a known volume of drug. The fluid delivery system utilizes a reservoir and a dispensing mechanism that dispenses the same volume of medicament upon each actuation. The heating system utilizes nichrome wire.

Claims

1. A control system for a handheld vapor delivery device, comprising: a circuit configured to provide a precise amount of power from a power source to heat a heating element to a minimum temperature required to fully vaporize a precise volume of liquid metered by a pressure generator, and to control a precise duration of supplying the precise amount of power to fully vaporize the precise volume of liquid at the required temperature to deliver a consistent and reliable dose by:

a. determining a precise amount of power required to vaporize the precise volume of liquid for the precise duration using the heating element;

b. metering a precise volume of liquid to the heating element;

c. supplying the precise amount of power from the power source to heat the heating element for the precise duration of time such that the combination of the precise amount of power and the precise duration of time heats the heating element to a minimum required temperature for a minimum required time to completely vaporize the precise volume of liquid;

d. monitoring the temperature of the heating element while supplying power;

e. comparing the temperature of the heating element to the desired minimum temperature; and

f. based on the comparing step, adjusting the precise duration or the precise amount of power to completely evaporate the liquid, wherein if the precise volume of liquid is adjusted, the precise duration or the precise amount of power is adjusted to completely evaporate the adjusted precise volume of liquid within a new required minimum temperature for a new required minimum time.

2. The control system of claim 1, wherein the circuit comprises a one shot circuit.

3. The control system of claim 1, wherein the circuit further comprises a processor programmed to monitor a resistance of a heating element and adjust an amount of power to a level sufficient to heat the heating element to a desired temperature.

4. The control system of claim 1, wherein the circuit includes a DC/DC boost converter and a supercapacitor operatively connected to the power source to regulate the amount of power to a level sufficient to heat the heating element to a desired temperature.

5. The control system of claim 1, wherein the circuit is configured to activate the power source a predetermined number of times.

6. A handheld medication delivery device, comprising:

a. a housing having a first end and a second end;

b. a mouthpiece attached to the first end;

c. a fluid delivery system;

d. a vaporization system comprising a heating element located between the mouthpiece and the fluid delivery system; and

e. a power control system including circuitry configured to provide a precise amount of power from a power source to heat the heating element to a minimum temperature required to fully vaporize a precise volume of liquid metered by a pressure generator, and to control a precise duration of time that the precise amount of power is supplied to fully vaporize the precise volume of liquid at the required temperature to deliver a consistent and reliable dose by:

(1) determining a precise amount of power required to vaporize the precise volume of liquid for the precise duration using the heating element;

(2) metering a precise volume of liquid to the heating element;

(3) supplying the precise amount of power from the power source to heat the heating element for the precise duration of time such that the combination of the precise amount of power and the precise duration of time heats the heating element to a minimum required temperature for a minimum required time to completely vaporize the precise volume of liquid;

(4) monitoring the temperature of the heating element while supplying power;

(5) comparing the temperature of the heating element to the desired minimum temperature; and

(6) based on the comparing step, adjusting the precise duration or the precise amount of power to completely evaporate the liquid, wherein if the precise volume of liquid is adjusted, the precise duration or the precise amount of power is adjusted to completely evaporate the adjusted precise volume of liquid within a new required minimum temperature for a new required minimum time.

7. The hand-held medicant delivery device of claim 6, wherein the power control system includes a one-shot circuit.

8. The handheld medication delivery device of claim 6, wherein the circuit includes a processor programmed to monitor a resistance of the heating element and adjust power until the heating element reaches the desired temperature.

9. The hand-held medicant delivery device of claim 6, wherein the power control system comprises a DC/DC boost converter operably connected to a supercapacitor.

10. The hand-held medicant delivery device of claim 6, wherein the circuit comprises a processor programmed to activate the power source a predetermined number of times.

11. The hand-held medicant delivery device of claim 6, wherein the power source is an alkaline battery.

12. The hand-held medicant delivery device of claim 6, wherein the fluid delivery system comprises:

a. a fluid reservoir inside the housing, the fluid reservoir having a first end and a second end; and

b. a pressure generator positioned inside a fluid reservoir at the second end of the fluid reservoir and configured to incrementally advance toward a first end of the fluid reservoir at a fixed and discrete distance to consistently meter the precise volume of liquid from the fluid reservoir.

13. The handheld medication delivery device of claim 12, wherein the fluid delivery system further comprises a cap in fluid communication with the fluid reservoir at a first end of the fluid reservoir, the cap having an outlet opposite the fluid reservoir, wherein when positive pressure is applied to the fluid reservoir, the fluid stored within the fluid reservoir can exit through the outlet to form a droplet at the outlet.

14. A hand-held medicant delivery device as recited in claim 13, wherein the outlet and the heating element are spaced apart by a distance less than the droplet such that the droplet can contact the heating element while still on the outlet.

15. The handheld medication delivery device of claim 13, wherein the pressure generator includes:

a. a piston contained in the fluid reservoir, the piston configured to push the liquid out through the cap; and

b. a fluid release actuator operably connected to the piston, wherein actuation of the fluid release actuator causes the piston to advance the fixed and discrete distance toward the first end of the fluid reservoir.

16. The handheld medication delivery device of claim 12, further comprising a permeable membrane positioned between the mouthpiece and the heating element, wherein the permeable membrane is permeable to vapor molecules of a predetermined size.

17. A handheld medication delivery device, comprising:

a. a housing having a first end and a second end;

b. a mouthpiece attached to the first end;

c. a fluid delivery system, the fluid delivery system comprising:

i. a fluid reservoir inside the housing, the fluid reservoir having a first end and a second end, an

A pressure generator positioned inside the fluid reservoir at a second end of the fluid reservoir and configured to incrementally advance toward a first end of the fluid reservoir at a fixed and discrete distance to consistently meter a precise volume of liquid from the fluid reservoir;

d. a vaporization system comprising a heating element located between the mouthpiece and the fluid reservoir; and

e. a control system to deliver power to the vaporization system;

wherein a consistent and reliable dose is delivered by:

(1) determining the precise amount of power required to vaporize the precise volume of liquid for a precise duration using the heating element;

(2) metering a precise volume of liquid to the heating element;

(3) supplying the precise amount of power from a power source to heat a heating element for the precise duration of time such that the combination of the precise amount of power and the precise duration of time heats the heating element to a minimum required temperature for a minimum required time to completely vaporize the precise volume of liquid;

(4) monitoring the temperature of the heating element while supplying power;

18. The handheld medication delivery device of claim 17, wherein the fluid delivery system further comprises a cap in fluid communication with the fluid reservoir at a first end of the fluid reservoir, the cap having an outlet opposite the fluid reservoir, wherein when positive pressure is applied to the fluid reservoir, the fluid stored within the fluid reservoir can exit through the outlet to form a droplet at the outlet.

19. A hand-held medicant delivery device as recited in claim 18, wherein the outlet and the heating element are spaced apart by a distance less than the droplet such that the droplet can contact the heating element while still on the outlet at the opening.

20. The handheld medication delivery device of claim 18, wherein the pressure generator comprises:

21. The handheld medication delivery device of claim 17, further comprising a permeable membrane positioned between the mouthpiece and the heating element, wherein the permeable membrane is permeable to vapor molecules of a predetermined size.

22. A method of efficiently and consistently vaporizing a precise volume of liquid medicant from a handheld device, comprising:

a. determining the precise amount of power required to vaporize a precise volume of the liquid for a precise duration using a heating element;

b. metering a precise volume of liquid to the heating element;

c. supplying the precise amount of power from a power source to heat a heating element for the precise duration of time such that the combination of the precise amount of power and the precise duration of time heats the heating element to a minimum required temperature for a minimum required time to completely vaporize a precise volume of the liquid metered by a pressure generator;

d. monitoring the temperature of the heating element while supplying power;

23. The method of claim 22, wherein metering a precise volume of the liquid comprises:

a. storing the liquid in a fluid reservoir; and

b. a precise amount of positive pressure is applied within the fluid reservoir to release a precise volume of fluid from the fluid reservoir.

24. The method of claim 23, wherein the precise amount of positive pressure is applied by incrementally advancing a threaded plunger a predetermined distance within the fluid reservoir.

25. The method of claim 24, wherein advancing the threaded plunger the predetermined distance is accomplished by turning a drive nut a fixed rotational displacement, wherein the threaded plunger includes a groove extending down a length of the threaded plunger, and an anti-rotation tang is sealed within the groove to prevent rotation of the threaded plunger.

26. The method of claim 25, wherein turning the drive nut is accomplished by activating a button that turns the drive nut the fixed rotational displacement each time the button is activated, wherein the drive nut is held in a fixed translational position.

27. The method of claim 22, wherein supplying the precise amount of power is accomplished by programming a processor to allow the power supply to be activated a predetermined number of times.

28. The method of claim 22, wherein monitoring the temperature of the heating element is accomplished by measuring the resistance of the heating element.

29. The method of claim 22, further comprising a super capacitor operably connected to the power source and processor to limit the amount of power supplied to produce a desired minimum temperature.

30. The method of claim 29, wherein the power source is an alkaline battery.

31. The method of claim 22, wherein supplying the power is initiated by creating an air flow at a mouthpiece of the handheld device.

32. The method of claim 31, further comprising controlling a size of vapor molecules of a vaporized liquid by placing a permeable membrane between the heating element and the mouthpiece, wherein the permeable membrane is permeable only to vapor molecules of a predetermined size.

33. A control system for a handheld vapor delivery device, comprising:

a. means for providing a precise amount of power from a power source to heat the coil to a minimum temperature required to completely vaporize a precise volume of liquid; and

b. means for controlling a precise duration of supplying the precise amount of power to completely vaporize the precise volume of liquid at the desired temperature;

wherein a consistent and reliable dose is delivered by:

(2) metering a precise volume of liquid to the heating element;

(4) monitoring the temperature of the heating element while supplying power;