Patent Application
20240197523
The present disclosure is related to a system and method that enables an injection into a cavity or a void, and in particular through a tissue into a cavity or void in a human body, such as the suprachoroidal space in ocular tissue.
The present disclosure is related to a device and method that enables delivery of multiple therapeutics to a cavity or a void of a human body, and in particular to ocular tissue in posterior segment of the eye through the suprachoroidal space. Posterior segment eye diseases are a major cause of permanent visual impairment affecting millions of people which can lead to blindness if left untreated. It includes multiple diseases such as age-related macular degeneration (AMD), diabetic retinopathy, diabetic macular edema (DME), choroideremia (CHM), retinal vein occlusion (RVO), uveitis, and endophthalmitis. Although pharmaceutical agents may be available to prevent disease progression in many cases, systemic delivery cannot achieve therapeutic concentrations in the posterior segment due to blood-eye barrier.
Recently, the suprachoroidal space (SCS) has been explored as the potential drug delivery route to the back of the eye. The suprachoroidal space is the potential space between the sclera and the choroid. Drug delivered in this space can go around the eye globe to the posterior segment of the eye. This route for drug delivery has been shown to be more effective for treatment of the posterior segment than intravitreal injections. However, the simplicity of intravitreal injection outweighs the surgical procedure previously needed for suprachoroidal delivery. Historically, suprachoroidal delivery was achieved by creating small incision using scalpel, followed by delivery using a needle or cannula. More recently, a microneedle with a predefined, short length, which allows penetration only up to certain depth, has been used to target suprachoroidal space. Because the scleral thickness varies significantly within the patient populations, either prior mapping of eye geometry, or trial and error, is necessary while injecting with hollow microneedles. If the needle is too long, it can easily penetrate through the thin suprachoroidal space to inject the drug in the vitreous; and, if it is too short, it delivers into the sclera. The sclera is 10 times stiffer than the choroid and 200 times stiffer than the retina making it even more challenging to pierce the sclera without injecting into the vitreous. In some instances, a small volume (on the order of 100 microliters) of therapeutic needs to be injected into the suprachoroidal space, and it needs to be injected with sufficient force to displace the positive resistance of intraocular pressure pressing the choroid against the sclera to achieve a broad coverage of the posterior segment of the eye. This may be difficult to achieve using a conventional hand-held syringe.
Accordingly, there is a need for an improved system and method for suprachoroidal drug delivery that precisely, consistently and safely targets the suprachoroidal space and provides broad coverage of the posterior segment of the eye.
According to some aspects of the present disclosure, there is provided an injection system comprising an injection assembly comprising a syringe barrel defining a lumen between a proximal end and a distal end and a second sealing element moveably disposed within the lumen to dispense an injection agent from an injection chamber defined in the syringe barrel, and a puncture element configured to deliver the injection agent into a space in a tissue of a patient. The tissue is less permeable to the injection agent than the space. The injection system also includes a support platform configured to support the injection assembly and anchor the injection assembly relative to a site of injection, a drive assembly configured to operate the injection assembly, one or more sensors configured to monitor one or more forces on the injection assembly, and a controller in communication with the one or more sensors to receive information about the one or more forces on the injection system. The controller is configured, based on the information, to operate the drive assembly to advance the puncture element through the tissue toward the space such that the injection agent remains in the injection chamber until the puncture element fluidly connects the injection chamber with the space.
In some embodiments, the injection assembly further includes a first sealing element moveably disposed within the lumen distal to the second sealing element, wherein the first sealing element and the second sealing element form a seal with the lumen and define the injection chamber between them. The puncture element can be in fluid communication with the injection chamber to deliver the injection agent from the injection chamber into a space in a tissue of a patient. When a force is applied on the second sealing element in a distal direction, in response to a first opposing force as the puncture element advances through the tissue, the first sealing element moves in the distal direction to advance the puncture element in the distal direction, without conveying the injection agent through the puncture element, and in response to a second opposing force when the injection chamber is fluidly connected to the space, the first sealing element remains stationary and the injection agent is conveyed from the injection chamber through the puncture element.
In some embodiments, the drive assembly is linked to the second sealing element to apply the force on the second sealing element to translate the second element in the distal direction. In some embodiments, the drive assembly comprises a linear actuator linked the second sealing element to apply the force on the second sealing element to translate the second element in the distal direction. In some embodiments, the drive assembly comprises a first driver configured to translate the syringe barrel relative to the support platform and a second driver linked to the second sealing element to translate the second sealing element relative to the syringe barrel. The one or more sensors can comprise a first load cell configured to measure force on the syringe barrel, and the one or more sensors can comprise a second load cell configured to measure force on the second sealing element. In some embodiments, the one or more sensors comprise one or more of a pressure sensor, force sensor, strain sensor, position sensor or low rate sensor.
In some embodiments, the controller is programmed to implement one or more feedback loops to monitor the first opposing force and the second opposing force. In some embodiments, the controller is programmed to implement one or more feedback loops to monitor a pre-insertion of the puncture element into the tissue, with the one or more feedback loops being configured to monitor an increase in force onto the puncture element, to detect a drop in force on the puncture element, and based on the drop, to cause an advancement of the puncture element by a pre-determined distance to imbed the puncture element into the tissue. In some embodiments, the controller is programmed to implement one or more feedback loops to monitor an advancement of the puncture element through the tissue, the one or more feedback loops being configured to measure a load on the second sealing element and detect a drop in the load once the puncture element reaches the space in the tissue. In some embodiments, the controller is programmed to implement one or more feedback loops to monitor an injection of the injection agent into the space, with the one or more feedback loops being configured to control a velocity or an advancement distance of the second sealing element. In some embodiments, the controller is programmed to cause a retraction of the puncture element by a pre-determined distance when the one or more sensors detect a drop in load on the second sealing element. In some embodiments, the controller is programmed to control a stopping distance of the puncture element as the puncture element enters the space.
In some embodiments, the tissue is conjunctiva and the space is subconjunctival space. In some embodiments, the tissue is sclera and the space is suprachoroidal space. In some embodiments, the tissue is sclera and choroid and the space is intravitreal space. In some embodiments, the tissue is cornea and the space is an anterior chamber of an eye.
In some aspects, the present disclosure provides an injection system that comprises an injection assembly comprising a syringe barrel defining a lumen between a proximal end and a distal end, a first sealing element and a second sealing element moveably disposed within the lumen. The second sealing element is distal to the first sealing element to define an injection chamber. A puncture element is fluidly connected to the injection chamber and configured to deliver an injection agent from the injection chamber into a space in a tissue of a patient. The tissue is less permeable to the injection agent than the space. The injection system also includes a support platform configured to support the injection assembly and anchor the injection assembly relative to a site of injection, a drive assembly configured to translate one or both of the syringe barrel or the second sealing element relative to the support platform, one or more sensors configured to monitor one or more forces on the injection assembly, and a controller in communication with the one or more sensors to receive information about the one or more forces on the injection system. The controller in communication with the one or more sensors receives information about the one or more forces on the injection system, and is configured to, based on the information, to control the drive assembly to advance the puncture element through the tissue toward the space such that when the drive assembly translates the second sealing element in a distal direction. In response to a first opposing force as the puncture element advances through the tissue, the first sealing element moves in the distal direction to advance the puncture element in the distal direction, without conveying the injection agent through the puncture element, and in response to a second opposing force when the injection chamber is fluidly connected to the space, the first sealing element remains stationary and the injection agent is conveyed from the injection chamber through the puncture element.
In some embodiments, the drive assembly is configured to translate independently of one another the syringe barrel and the second sealing element relative to the support platform. In some embodiments, the drive assembly is linked to the second sealing element to apply the force on the second sealing element to translate the second element in the distal direction. In some embodiments, the drive assembly comprises a linear actuator linked the second sealing element to apply the force on the second sealing element to translate the second element in the distal direction. In some embodiments, the drive assembly comprises a first driver configured to translate the syringe barrel relative to the support platform and a second driver linked to the second sealing element to translate the second sealing element relative to the syringe barrel.
In some embodiments, the one or more sensors comprise a first load cell configured to measure force on the syringe barrel. In some embodiments, the one or more sensors comprise a second load cell configured to measure force on the second sealing element. In some embodiments, the one or more sensors comprise one or more of a pressure sensor, force sensor, strain sensor, position sensor or low rate sensor.
In some embodiments, the controller is programmed to implement one or more feedback loops to monitor the first opposing force and the second opposing force. In some embodiments, the controller is programmed to implement one or more feedback loops to monitor a pre-insertion of the puncture element into the tissue. The one or more feedback loops can be configured to monitor an increase in force onto the puncture element, to detect a drop in force on the puncture element, and based on the drop, to cause an advancement of the puncture member by a pre-determined distance to imbed the puncture element into the tissue. In some embodiments, the controller is programmed to implement one or more feedback loops to monitor an advancement of the puncture element through the tissue, with the one or more feedback loops being configured to measure a load on the second sealing element and detect a drop in the load once the puncture element reaches the space in the tissue. In some embodiments, the controller is programmed to implement one or more feedback loops to monitor an injection of the injection agent into the space, with the one or more feedback loops being configured to control a velocity or an advancement distance of the second sealing element. In some embodiments, the controller is programmed to cause a retraction of the puncture element by a pre-determined distance when the one or more sensors detect a drop in load on the second sealing element. In some embodiments, the controller is programmed to control a stopping distance of the puncture element as the puncture element enters the space.
In some embodiments, the tissue is conjunctiva and the space is subconjunctival space. In some embodiments, the tissue is sclera and the space is suprachoroidal space. In some embodiments, the tissue is sclera and choroid and the space is intravitreal space. In some embodiments, the tissue is cornea and the space is an anterior chamber of an eye.
A method of delivering an injection agent is provided that comprises inserting a puncture element into a tissue. The puncture element can be configured to deliver an injection agent from an injection chamber into a space in the tissue, with the tissue having a density greater than the space such that the tissue is less permeable to the injection agent than the space. The method also includes advancing, using a drive assembly, the puncture element through the tissue toward the space, monitoring one or more forces on the puncture element using one or more sensors, and controlling, using a controller in communication with the one or more sensors, the drive assembly to advance the puncture element through the tissue toward the space such that the injection agent remains in the injection chamber until the puncture element fluidly connects the injection chamber with the space.
In some embodiments, the puncture element is positioned on a distal end of an injection assembly comprising a syringe barrel defining a lumen between a proximal end and a distal end and a first and second sealing element moveably disposed within the lumen to dispense the injection agent from the injection chamber. In some embodiments, in response to a first opposing force of the one or more force on the puncture element as it advances through the tissue, the first sealing element moves in a distal direction to advance the puncture element in the distal direction, without conveying the injection agent through the puncture element. In some embodiments, in response to a second opposing force of the one or more forces on the puncture element when the injection chamber is fluidly connected to the space, the first sealing element remains stationary and the second seal element moves in a distal direction such that the injection agent is conveyed from the injection chamber through the puncture element into the space.
In some embodiments, the tissue is conjunctiva and the space is subconjunctival space. In some embodiments, the tissue is sclera and the space is suprachoroidal space. In some embodiments, the tissue is sclera and choroid and the space is intravitreal space. In some embodiments, the tissue is cornea and the space is an anterior chamber of an eye.
A method of delivering an injection agent is provided that comprises positioning an injection assembly adjacent a tissue. The injection assembly comprises a syringe barrel defining a lumen between a proximal end and a distal end and a second sealing element moveably disposed within the lumen to dispense an injection agent from an injection chamber defined in the syringe barrel, and a puncture element extending configured to deliver the injection agent into a space in the tissue. The tissue has a density greater than the space such that the tissue is less permeable to the injection agent than the space. The method also includes monitoring one or more forces on the injection assembly using one or more sensors, and controlling the injection assembly using the forces on the injection system using a controller in communication with the one or more sensors to advance the puncture element through the tissue toward the space such that the injection agent remains in the injection chamber until the puncture element fluidly connects the injection chamber with the space.
In some embodiments, in response to a first opposing force of the one or more force on the puncture element as it advances through the tissue, the first sealing element moves in a distal direction to advance the puncture element in the distal direction, without conveying the injection agent through the puncture element. In some embodiments, in response to a second opposing force of the one or more forces on the puncture element when the injection chamber is fluidly connected to the space, the first sealing element remains stationary and the second seal element moves in a distal direction such that the injection agent is conveyed from the injection chamber through the puncture element into the space. In some embodiments, the method further comprises anchoring the injection assembly relative to a site of injection in the tissue.
In some embodiments, the tissue is conjunctiva and the space is subconjunctival space. In some embodiments, the tissue is sclera and the space is suprachoroidal space. In some embodiments, the tissue is sclera and choroid and the space is intravitreal space. In some embodiments, the tissue is cornea and the space is an anterior chamber of an eye.
The present disclosure is further described in the detailed description which follows, in reference to the noted plurality of drawings by way of non-limiting examples of exemplary embodiments, in which like reference numerals represent similar parts throughout the several views of the drawings, and wherein
While the above-identified drawings set forth presently disclosed embodiments, other embodiments are also contemplated, as noted in the discussion. This disclosure presents illustrative embodiments by way of representation and not limitation. Numerous other modifications and embodiments can be devised by those skilled in the art which fall within the scope and spirit of the principles of the presently disclosed embodiments.
The present disclosure provides a motorized injection system for delivery of a therapeutic agent into a potential space or cavity in tissue. In some embodiments, such systems can be used for drug delivery to the suprachoroidal space. In some embodiments, such systems are automated and comprise of sensors and feedback loops. The systems of the present disclosure can thus be configured to precisely, consistently and safely target the suprachoroidal space and to provide broad coverage of the posterior segment of the eye.
In some embodiments, the injection system comprises a syringe barrel for holding one or more injection agents, a penetrating element (also referred as needle, but similar devices can be used) attached to the syringe barrel in fluid communication with the syringe barrel and a sealing element (also referred as a pushing plunger) to expel injection agent from the syringe barrel through the needle. As described in more detail below, the injection system can include a regular syringe or an auto-stop syringe with multiple sealing elements as described in more detail below.
In reference to
In some embodiments, the injection system may include a syringe comprising a syringe barrel defining a medicament chamber for storing a therapeutic agent, a needle 15 in fluid communication with the medicament chamber to administer the therapeutic agent from the medicament chamber, and a plunger 11 slidably disposed within the syringe barrel and being configured to expel the therapeutic agent from the medicament chamber through the needle 15.
In some embodiments, a standard syringe can be used, such that the medicament chamber can have a volume of between about 0.1 ml and 20 ml, but larger or smaller syringes can also be used. In some embodiments, the medicament chamber can have a volume of approximately 0.1 ml, 0.5 ml, 1 ml, 3 ml, 5 ml, or 10 ml prior to the displacement of the fluid.
In some embodiments, the needle may be a standard needle between 34 G and 25 G. In some embodiments, the needle may be a standard 30 G needle. Various needle sizes can be used to deliver therapeutic treatment to the SCS, as discussed above. In some embodiments, particularly for higher viscosity formulations, for example, greater than 10 centipoise, needles with larger lumens may be used. The pre-insertion step required to block the fluid flow may set a limit to the range of needle lumen diameter and bevel size that can be used effectively to target the SCS. In some embodiments, with a minimal human scleral thickness in mind, optimal results can be obtained by limiting the pre-insertion depth to less than or equal to approximately 0.5 millimeters (for example, between about 0.05 mm to 0.5 mm) if the needle is inserted perpendicular to the scleral surface. If inserted at an angle other than perpendicular, one can sufficiently insert a needle with longer bevel without piercing through the sclera. For example, based on geometrical correlation, a 30-gauge needle with the standard bevel (angle: 12 degrees, length: 1.45 mm) inserted at an angle less than or equal to approximately 20° to the surface will reach less than 0.5 millimeters deep when measured normally from the surface. Similarly, larger needles with longer bevel lengths can also be used. Shorter bevels allow for a greater range in angles of pre-insertion for a given needle size. Broadly speaking, needles with outer diameters smaller than the scleral thickness of approximately 0.5 millimeters are readily usable to access the SCS and the angle of needle insertion is determined based on the beveled tip length. In some embodiments, the volume of the medicament chamber is between 20 and 200 microliters. For improved haptics and signal to noise ratio for the distance tracking elements, in some embodiments, the stroke length of the pushing plunger to deliver the therapeutic fluid or suspension is at least 1 centimeter in length. For some embodiments, the flow rate of injection is targeted to be between 0.2 and 20 microliters per second on average. In some embodiments, the syringe barrel is lined in silicone oil, silicone rubber, rubber, glass, polytetrafluorethylene, or polypropylene to minimize adsorption of the therapeutic to the syringe barrel inner surface.
In some embodiments, the friction between the syringe barrel and the plunger can be designed to optimize the performance of the system. For example, the system can be sized such that the static and kinetic friction coefficient are approximately equal so that there is no unintended acceleration of the needle. On the other hand, the static friction coefficient can be higher than the kinetic friction coefficient so that after the needle stops in the cavity, if it has a high force barrier to overcome. High static friction of the needle plunger also allows for high fluid flow rates during injection while maintaining the needle tip position. In some embodiments, the needle-plunger-kinetic-friction is high enough to arrest the needle motion as soon as the lumen is exposed to the cavity. However, the kinetic coefficient can still be limited such that the internal pressure inside the syringe barrel is not so high as to result in a break-down of or injury to the tissue.
In reference to
In some embodiments, the linear actuator may be a mechanical actuator comprising for example, a lead screw and a nut or gear driven by an electric motor, but other designs may be used. In some embodiments, pneumatic, hydraulic, electromechanical, magnetic or other types of linear actuators may also be used. In some embodiments, a single actuator may be used to drive both the syringe barrel and the plunger. Different motion of the syringe barrel and the plunger can be achieved by engaging/disengaging gear mechanism. In some embodiments, linear motion of the pushing plunger can be accomplished by applying hydraulic pressure.
In reference to
In some embodiments, the motorized system of the present disclosure includes a plurality of sensors that can measure one or more parameters throughout the injection process. The one or more sensors may communicate with the controller to implement one or more feedback loops to control various steps of the injection process. Various types of sensors or other mechanisms can be used to control the injection steps, including but not limited to load cells and sensors, such as pressure sensors, strain sensors, and/or force sensors, as will be discussed in more detail below.
In some embodiments, the load that the drive assembly applies onto the syringe barrel and onto the pushing plunger may be measured and communicated to the controller. In some embodiments, the load can be measured using one or more load cells. Such load cells can be embedded in or otherwise configured to receive a signal from the needle, the needle plunger, the pushing plunger or both. In some embodiments, such load may be measured by the torque experienced by the motor based on its correlation to the current drawn by the motor. In some embodiments, the motorized injection system may further include one or more sensors to monitor the position or movement of the injection system as the whole or the syringe barrel or the plunger individually. Such information may be used, for example, to determine the distance travelled by the injection system, the syringe barrel, or the plunger, the needle plunger, in combination or individually. In some embodiments, the motorized system may include one or more sensors to monitor the position or speed at which the syringe barrel or the plunger, in combination or individually, as they move. For example, such information may be used to control the flow rate of the therapeutic agent or to prevent the pushing plunger from overshooting the desired injection volume. In some embodiments, the flowrate may be monitored using a high precision flow sensor including microfluidic mass flow sensors.
In some embodiments, the system of the present disclosure can also measure the pressure in the syringe. In some embodiments, the pressure can be measured indirectly by monitoring the load on the plunger. In some embodiments, the system can be configured such that both the kinetic and static frictions coefficients between the plunger and the syringe barrel are close to 1 to sense the fluid pressure more accurately. In some embodiments, the motorized injection system may further include one or more pressure sensors, force sensors, or strain sensors for a direct measurement of the pressure of the therapeutic agent in the medicament chamber.
In some embodiments, the relative position of the pushing plunger to either the needle plunger in the case of an auto-stop syringe or the needle hub in the case of a standard syringe, is monitored to determine the volume of therapeutic drawn into the syringe or injected into the cavity. In some embodiments the distance of travel measured following pre-insertion can have limits set so as to minimize the chances of overshoot.
In some embodiments, one or more feedback loops may be implemented based on the load distributions during Stages I-III-a (as discussed above in connection with
Various embodiments of the present disclosure may include one or more feedback loops discussed above depending on the design of the system or the level of control desired by the user, among other considerations.
In some embodiments, a regular syringe may be used in the motorized injection system of the present disclosure. Such syringe can include a syringe barrel for holding one or more injection agents, a needle attached to the syringe barrel in fluid communication with the barrel and a plunger to expel injection agent from the syringe barrel through the needle.
In some embodiments, an adjustable injection system (also referred to as an auto-stop injection system) that automatically self-adjusts the depth the needle penetrates into the tissue/cavity can be used. In reference to
A movable needle 308 is supported by the needle plunger so that the movement of the needle plunger may also move the needle, the needle being in fluid communication with the medicament chamber to deliver a therapeutic agent from the medicament chamber to the patient. The needle can be connected to the needle plunger using multiple techniques. In some embodiments, the needle is inserted into the rubber plunger and secured with waterproof adhesive. In some embodiments, the plunger could be molded around the needle. In some embodiments, a needle with threads on the outer surface could be screwed into the plunger.
An exemplary auto-stop syringe for use to deliver therapeutic agents into the suprachoroidal space is disclosed in U.S. application Ser. No. 16/469,567, filed Jun. 13, 2019 and PCT Application PCT/US2020/051702, filed on Sep. 20, 2020, all of which are incorporated by reference herein in their entireties. In some embodiments, such design variables as the syringe geometry, needle geometry, flow rate, viscosity, and frictional forces are related and can be designed as discussed in Chitnis, G. D., Verma, M. K. S., Lamazouade, J. et al. A resistance-sensing mechanical injector for the precise delivery of liquids to target tissue. Nat Biomed Eng 3, 621-631 (2019), which is incorporated herein in its entirety. In some embodiments, the insertion force can be taken into account to select various design variables. As a result, the system is capable of delivering drug and gene therapies that benefit from localization to the SCS including those that treat diseases and disorders of the choroid and the retina. It should be noted that while the present disclosure describes the instant injection system in connection with drug delivery to the SCS cavity, the presently disclosed systems and methods can be used to deliver therapeutic agents to other voids or cavities of the human body.
In some embodiments, the auto-stop syringe is pre-filled with a therapeutic. In some embodiments, the therapeutic is contained in one or more vials, which interface via a rapid fill port to the syringe barrel (for example, as described in co-pending PCT Application PCT/US2020/051702, filed on Sep. 20, 20201, incorporated herein by reference in its entirety) in which any valves that are manually turned during operation in the previous filling could be motorized or use a solenoid valve in this filling.
Either prior to filling with a therapeutic or after filling with a therapeutic, depending on whether the filling process is automated, the motorized injection system can be connected to the head and/or eye of the patient. In some embodiments, an adjustable headband can be secured around a patient's head. In some embodiments, the distal end of the motorized injection system can be anchored to external landmarks around the ocular orbit.
The position of the motorized injection system can be adjusted to achieve a desired angle of needle insertion, which would depend on the bevel, to embed the lumen into the tissue. Once the motorized injection system is in place, the tip of the needle can be located near the surface of the sclera, for example, within about 2 centimeters, within about 1 centimeter, or within about 0.5 centimeters from the surface of the sclera. In some embodiments, such distance can be between about 0.1 and about 2 cm, about 0.1 and about 1 cm, or about 0.1 and about 0.5 cm. In some embodiments, an acoustic or laser range finder may be used to assist with the initial positioning of the needle tip. Next, the user provides a signal via a button or touch screen to initiate the injection process.
By way of a non-limiting example, the use of the motorized injection system with an auto-stop syringe is described in reference to
In reference to
Once the needle is imbedded into the sclera, the movement of the syringe barrel is stopped, and the pushing plunger is advanced in the syringe barrel to pressurize the contents of the syringe barrel. In some embodiments, the pushing plunger is advanced a pre-specified or user-specified distance or until a pre-specified or user-specified load is reached on the load cell attached to the pushing plunger or its fixture confirming that the lumen of the needle is fully imbedded in the sclera. In some embodiments, this step is skipped.
In some embodiments, an optional elastomer contact pad 320 can be used to prevent eye rolling pressed against sclera by an operator of the device, such as a physician. This can allow the relative angle of injection to be controlled.
In reference to
In reference to
In reference to
After the therapeutic agent has been delivered to the SCS, the user can remove the syringe needle from the eye. In some embodiments, the syringe can be removed manually. In some embodiments, the entire auto-stop syringe is retracted away from the eye until the needle is no longer contacting the sclera. This can be achieved by returning the auto-stop syringe to the starting positions, or by returning at least to the point at which the needle tip had initially sensed an increase in load, corresponding with contacting the scleral surface.
In some embodiments, one or more feedback loops can be used to monitor the operations of an auto-stop syringe. In some embodiments, a first feedback loop can monitor the pre-insertion of the needle into the sclera. For example, during insertion of needle into the sclera (movement of the complete syringe towards the eye), a load cell attached to the needle or syringe barrel can register increasing force until the needle punctures the sclera. On puncture, there is a drop in load and the needle is further then advanced a pre-determined distance until the lumen of the needle is imbedded into the sclera and then discontinues advancing the complete syringe.
In some embodiments, a second feedback loop can be provided to monitor the advancement of the needle through the sclera. For example, once the needle pre-insertion is complete, the syringe barrel is locked in place and the pushing plunger advances while the load on the pushing plunger is measured. The load increases on the pushing plunger and may plateau as the needle advances through the sclera. The load falls once the needle lumen reaches the SCS.
In some embodiments, a third feedback loop may be provided to monitor the injection of the therapeutic agent into the SCS. For example, the pushing plunger can be advanced at a pre-specified velocity until a specific distance (correlating to a desired injection volume) is reached, or until the pushing plunger reaches the needle plunger to avoid needle overshoot.
As described in more detail in
Once the syringe barrel load cell shows an increase in load, the syringe barrel position is locked and pushing plunger is moved forward relative to the syringe in step 414. In step 416, if the pushing plunger load cell is showing load higher than the force needed to inject in SCS, then the pushing plunger is moved forward relative to the syringe (step 414). If the pushing plunger load cell is not showing load higher than the force to inject in SCS, then in step 418 the pushing plunger can continue to be pushed forward. If the load is similar to the force needed to inject in SCS or if a drop in internal pressure is detected, note the position of the pushing plunger so the distance moved by the pushing plunger can be monitored, which can be used, for example, to prevent the pushing plunger from bumping into the needle plunger or to monitor the amount of the injection agent delivered to SCS.
In step 420, if the force measured by the pushing plunger load cell is maintained as the pushing plunger moves forward, then it is determined whether or not the pre-determined amount of therapeutic has been delivered based on the position of the pushing plunger (step 422). If it has not, then the system continues to push the pushing plunger forward (step 418). If it has, then the system stops pushing the pushing plunger forward (step 426). If the force measured by the pushing plunger load cell is not maintained as the pushing plunger is moved forward (step 420), then in step 424, if the load increases significantly, it indicates all the therapeutic is delivered and the pushing plunger is at the end of the injection chamber. The system then stops moving the pushing plunger forward (step 426).
By way of a non-limiting example, the use of the motorized injection system with an auto-stop syringe is described in reference to
In reference to
In reference to
In reference to
In reference to
In reference to
After the therapeutic agent has been delivered to the SCS, the user can remove the syringe needle from the eye. In some embodiments, the syringe can be removed manually. In some embodiments, the entire syringe is retracted away from the eye until the needle is no longer contacting the sclera. This can be achieved by returning the syringe to the starting positions, or by returning at least to the point at which the needle tip had initially sensed an increase in load, corresponding with contacting the scleral surface.
In some embodiments, one or more feedback loops can be used to monitor the operations of an auto-stop syringe. In some embodiments, a first feedback loop can be provided to monitor the insertion of the needle into the sclera. For example, when the needle is pre-inserted into the sclera (movement of the complete syringe towards the eye), a load cell attached to the needle or syringe barrel registers increasing force until the needle punctures the sclera, but then there is a drop in load. After the drop is detected, the needle can then be advanced a pre-determined distance until the lumen of the needle is imbedded into the sclera and the syringe barrel can be stopped. In some embodiments, a second feedback loop can be provided to pressurize the contents of the syringe barrel. For example, once the pre-insertion is complete, the syringe barrel is locked in place and the pushing plunger advances while the load on the plunger or the pressure of the therapeutic agent is measured until a pre-specified load, distance or pressure is reached to pressurize the therapeutic agent. In some embodiments, a third feedback loop is provided to monitor the load on the needle as it is being advanced through the sclera. In some embodiments, the load on the needle can be monitored indirectly. For example, once the fluid contents of the syringe are pressurized, the entire syringe is advanced until the load drops on the pushing plunger, indicating that the lumen of the syringe has reached the SCS. In some embodiments, when the needle is fixed to the hub of the syringe, the load on the syringe can be monitored since such load is indicative of the load on the needle. In some embodiments, once the cavity is reached, a fourth feedback loop can be used to deliver the therapeutic agent to the SCS. For example, once the needle enters the SCS, the plunger is then advanced at a pre-specified velocity until a specific distance (correlating to a desired injection volume) is reached, or until the pushing plunger reaches the needle plunger to avoid needle overshoot.
As described in more detail in
In step 614, the pushing plunger is pushed to pressurize the internal fluid by a known amount, and in step 616, both the syringe and the pushing plunger are moved to move the entire syringe. In step 618, it is determined whether the pushing plunger load cell is showing a drop in internal pressure. If it has, and if the load is similar to the force needed to inject in SCS or if a drop in internal pressure is detected, note the position of the pushing plunger and continue pushing the pushing plunger forward (step 620). If it has not, move both the syringe and the pushing plunger to move the entire syringe (step 616).
In step 622, if the force measured by the pushing plunger load cell is maintained as the pushing plunger moves forward, then it is determined whether or not the pre-determined amount of therapeutic has been delivered based on the position of the pushing plunger (step 624). If it has not, then the system continues to push the pushing plunger forward (step 626). If it has, then the system stops pushing the pushing plunger forward (step 628). If the force measured by the pushing plunger load cell is not maintained as the pushing plunger is moved forward (step 622), then in step 626, if the load increases significantly, it indicates all the therapeutic is delivered and the pushing plunger is now in direct contact with needle plunger. The system then stops moving the plunger forward (step 628).
In particular, in some embodiments, In step 614, the plunger is pushed to pressurize the internal fluid by a known amount, and in step 616, both the barrel and the plunger are moved to move the entire syringe. In step 618, internal fluid pressure gets checked continuously. If the load cell shows drop in pressure, note the position, hold the position of the barrel and continue pushing forward on the plunger to deliver the therapeutic in the SCS space. In step 618, if the plunger load cell has not yet registered a drop in load, then the entire syringe is advanced. When the plunger load cell does register a drop in load, the syringe barrel ceases advancing, and only the pushing plunger is advanced, in step 620. The pushing plunger load cell continues to be monitored, step 622. While load on the pushing plunger is monitored, the pushing plunger advances, delivering the therapeutic until the desired volume of the therapeutic has been delivered, step 624, stopping the advancement of the pushing plunger, step 628. Alternatively, the pushing plunger load cell registers an increase in load indicating that the pushing plunger has reached the distal portion of the syringe, step 626, stopping the advancement of the pushing plunger, step 628.
In some embodiments, in reference to
In this way, when the lumen of the needle reaches the SCS, as denoted by a drop in load on the pushing plunger load cell, the syringe barrel can then be locked in place, and the syringe plunger can be advanced, directly injecting the therapeutic into the SCS, essentially creating an auto-stopping needle from a standard syringe, when used in combination with the syringe driver. In such embodiments, a feedback loop may be provided to monitor the movement of the needle through the sclera. In some embodiments, the syringe barrel is not locked in place on reaching the SCS, and the needle remains in the cavity as the pushing plunger is advanced due to the drop in fluid resistance at the lumen of the needle. For example, after the syringe barrel contents are pressurized, the mechanical stop on the syringe barrel is released. Then the plunger is advanced, which advances the needle tip through the sclera until it reaches the SCS. Once there, the needle will automatically stop, as the pressure inside the syringe barrel is reduced by the egress of fluid from the needle tip into the SCS.
As described in more detail in
Once the syringe load cell shows an increase in load, step 814 includes pushing on the pushing plunger without any axial movement restrictions on syringe, and both the syringe and the pushing plunger move forward. In step 816, if the pushing plunger load is similar to the force needed to inject in SCS or if a drop in internal pressure is detected, note the position of the pushing plunger and continue pushing the pushing plunger forward. Optionally, the system may continue pushing the pushing plunger forward, while the syringe may be locked (step 818). If the pushing plunger load cell is not showing a drop in internal pressure, then the pushing plunger is pushed on as indicated in step 814.
In step 820, if the force measured by the pushing plunger load cell is maintained as the pushing plunger moves forward, then then it is determined whether or not the pre-determined amount of therapeutic has been delivered based on the position of the pushing plunger (step 822). If it has not, then the system continues to push the pushing plunger forward while the syringe position is locked (step 818). If it has, then the system stops pushing the pushing plunger forward (step 826). If the force measured by the pushing plunger load cell is not maintained as the pushing plunger is moved forward (step 820), then in step 824, if the load increases significantly, it indicates all the therapeutic is delivered and the pushing plunger is now in direct contact with the distal end of the syringe. The system then stops moving the pushing plunger forward (step 826).
A graphical user interface is included in some embodiments. For example, such user interface may allow the user to start the injection, monitor the injection through Stages I-III-b, and to abort the injection as necessary. In some embodiments, there is also a means of providing auditory feedback to the user. In some embodiments, lights, a graphical display and/or sounds are used as an indicator to denote one or more of the following events: setting the angle of insertion, filling the syringe with therapeutic, priming the syringe to get rid of any trapped air, turning on the device, advancing the needle towards the sclera, when the sclera is punctured, when the SCS is reached, when the therapeutic has been delivered, when the needle has been withdrawn from the eye.
In some embodiments, the GUI allows the user to input certain patient parameters including Intra-ocular pressure, scleral thickness, eye size etc. In some other embodiments, the GUI asks for patient information and generates a report after completing injection, and in further embodiments the patient information is obtained via one- or two-dimensional barcode scanner or near field scanner (NFC—Near Field Communication). In some embodiments, the injector can connect to an external server to upload this information and/or download relevant information for the case such as, disease being treated, prescribed therapeutic, and dosage information.
In some embodiments, a display on the motorized syringe driver is used to display instructions to the user and request input from the user as to when to advance to the next step of the injection process beginning with filling the syringe and ending with completion of the SCS injection. In some embodiments, the GUI also allows the user to input injection process parameters, such as, for example, the distance traveled by the system or its component, thresholds for pressure or load on the system or its components, volume of therapeutic to be loaded, volume of therapeutic to be delivered, flow rate of injection, duration of injection, angle of injection, or maximum travel distance of the needle following scleral puncture. In some embodiments, the user can select the desired volume and/or rate of injection. In some embodiments, the position of the pushing plunger, the needle tip and/or the floating plunger are displayed, and/or the load sensed by the needle tip load cell and/or the pushing plunger load cell.
In some embodiments, there is a camera focused on the surface of the tissue that provides a real-time magnified video picture on the display to the user so that they can witness the piercing of the sclera and ultimate withdrawal of the needle. In some embodiments, the camera can assist with the pre-insertion, where the user manually preinserts the needle tip and then activates automated system to complete delivery of the therapeutic agent to the cavity. In some embodiments, the injector may include a scanner for one or two dimensional bar codes to log the disposable syringe and therapeutic used to inject.
As discussed above, in some embodiments, the motorized injection system of the present disclosure can be equipped with one or more safety features to limit or control the needle over-shoot. In some embodiments, additionally or alternatively, the needle overshoot can be controlled by controlling the stopping distance of the needle plunger. The stopping distance is the distance the needle plunger travels after the needle-lumen reaches the cavity and begins the delivery of the therapeutic agent. The stopping distance is determined by how quickly the pressure in the syringe barrel drops below the frictional resistance of the needle plunger. Such distance can be characterized as a relationship (analogous to flow through a hollow needle is characterized by the Hagen-Poiseuille equation) between the frictional resistance of the needle plunger, needle inner diameter, needle length, needle bevel, syringe inner barrel diameter, formulation viscosity, force applied to the pushing plunger, mechanical properties of the device components. In some embodiments, the stopping distance may be predicted as a function of the time needed to drop the pressure and speed at which the needle was traveling. The stopping distance can be dependent on the volumetric elasticity of the syringe assembly and compressibility of the fluid. In some embodiments, the overshoot due to the stopping distance can be controlled by using one or more safety features described above. In some embodiments, the stopping distance can depend on the time required to implement and actuate the motorized feedback loop. As long as some portion of needle opening overlaps with the SCS, the payload will be delivered to the SCS. Hence acceptable stopping-distance is directly related to lumen size and bevel. For example, a 30 G needle with 0.160 mm lumen diameter, with a standard 12° bevel angle can overshoot by ˜0.8 mm while maintaining lumen-contact with SCS. For optimal fluid flow and maximizing overlap between the lumen and the SCS, the needle should be positioned such that the SCS is placed centrally to the lumen geometry, i.e., for the 30 G needle with 12° bevel angle, ˜0.4 mm stopping distance would position the SCS centrally to lumen. A stopping distance less than 0.4 mm is also acceptable.
In some embodiments, the stopping distance overshoot is corrected by having the motorized syringe driver retract the barrel of the syringe to ensure SCS is placed centrally to the lumen geometry. For example, for a 30 G needle with 12° bevel angle, if the stopping distance is more than 0.4 mm, the needle may be retracted back to place it centrally. In some embodiments, the barrel of the syringe is retracted a fixed distance to counter the volumetric elasticity of the syringe assembly and compressibility of the fluid. In other embodiments, the retraction distance incorporates the position of the syringe barrel when the load drop on the pushing plunger is first detected after traversing the sclera. In some embodiments, the retraction distance utilizes the measured deformation of the sclera in response to contact by the needle prior to puncture. In some embodiments, the retraction distance utilizes the known or measured time required to detect and implement the syringe stopping motorized feedback loop.
In some embodiments, the auto-stop syringe of the present disclosure may be pre-filled with the therapeutic agent during manufacturing, as described above. In some embodiments, the auto-stop syringe of the present disclosure may be filled with the therapeutic agent in the doctor's office, compounding pharmacy or surgical suite prior to the administration of the therapeutic agent to the patient. In some embodiments, the therapeutic agent may be provided in a vial for storage and may be transferred to the SCS system by the user only when the therapeutic agent is ready to be administered to the patient.
In some embodiments, as shown in
In some embodiments, when the needle plunger is set in its initial position and the pushing plunger is brought in contact with the needle plunger, the rapid fill port is fluidly connected to the syringe barrel at the site between the sealing elements. Connected to the passageway, partially or fully disposed within it, is a side port fill needle 906 (preferably larger than the injection puncture element, such as an 18 gauge puncture element). Such fill needle can be beveled to pierce the elastomer cap 903 of the therapeutic containing vial 902. In some embodiments, the fill puncture element of the rapid fill port can have its opening on the side of the fill puncture element rather than at the tip. This side port can be covered by a casing or self-sealing puncture membrane 908 that blocks fluid flow when in the closed position. The casing 908 can be disposed within the receptacle and can be biased by a spring 910 to close the port of the fill needle when the vial is not present in its receptacle. In some embodiments, the safety cap 118 may be configured to provide an airtight seal when attached to the injection system.
In operation, as shown in
Once the auto-stop syringe is loaded with a desired amount of the therapeutic agent, the vial can be removed from the receptacle of the rapid fill port, which allows the sliding fill needle casing to come up to seal the side port of the fill needle, which also seals the syringe barrel. The safety cap can be removed to allow fluid flow through the injection needle. The drive assembly can be activated to advance the pushing plunger until fluid appears at the tip of the injection needle indicating that the injection needle has been cleared of air. Then the auto-stop syringe is ready for use. This rapid fill port design can enable filling the auto-stop syringe with a therapeutic agent in a physician's office while maintaining sterility outside of a sterile facility.
In some embodiments, the auto-stop syringe of the present disclosure can be backfilled with the therapeutic agent. This can take place during the initial manufacturing of the syringe or at a physician's office immediately prior to use.
In some embodiments, as shown in
In some embodiments, as shown in
In some embodiments, as shown in
In some embodiments, as shown in
In some embodiments, the injection system of the present disclosure is used to deliver a viral gene delivery vector or vectors, including, but not limited to adeno-associated virus (AAV), a variant or serotype thereof, including but not limited to AAV serotypes 1-11, particularly AAV1, AAV2, AAV3, AAV4, AAV5, AAV6, AAV7, AAV8, AAV9, AAV10 and AAV11, and recombinant serotypes such as Rec2 and Rec3 to treat a genetic disorder of disease of the retina or choroid. AAV1, AAV2, AAV4, AAV5, AAV6, AAV7, AAV8, and AAV9 can all display tropism for retinal tissue, including retinal pigment epithelium and photoreceptors, as described in https://www.retinalphysician.com/issues/2020/special-edition-2020/vector-considerations-for-ocular-gene-therapy, incorporated herein by reference in its entirety. Exemplary diseases can include, but not limited to wet age-related macular degeneration, dry age-related macular degeneration (AMD), glaucoma, choroideremia, and other heritable vision diseases and disorders. In some embodiments, the injection system is used to deliver a viral delivery vector or vectors, including, but not limited to AAV, or a variant thereof, to transfect retinal and/or choroidal cells, such as including, but not limited to, photoreceptors, pigmented cells, bipolar cells, ganglion cells, horizontal cells, and amacrine cells, vascular endothelial cells, vascular smooth muscle cells, non-vascular smooth muscle cells, melanocytes, fibroblasts, resident immunocompetent cells, with anti-vascular endothelial growth factor (anti-VEGF), and anti-vascular endothelial growth factor receptor (anti-VEGFR) gene that when transcribed produces an anti-VEGF protein or proteins for treating wet AMD. In some embodiments, the gene therapy compositions may also include a promoter for the gene of interest.
In some embodiments, the injection system is used to deliver gene therapies including, but not limited to small interfering ribonucleic acids (siRNAs), short hairpin ribonucleic acids (shRNAs), micro-ribonucleic acids (microRNAs), closed end-deoxyribonucleic acids (ceDNAs), polymer-DNA conjugates, or clustered regularly interspaced short palindromic repeats (CRISPR) and CRISPR-associated protein 9 (Cas9) systems, and variants thereof, and transcription activator-like effector nucleases (TALENs) and variants thereof, and zinc finger nucleases (ZFNs) and variants thereof and transposon-based gene delivery such as the Sleeping Beauty (SB), piggyBac (PB), Tol2 or variants thereof. These gene therapies can be packaged in viral vectors, non-viral vectors or nanoparticles.
In some embodiments, the injection system is used to deliver a viral gene delivery vector or vectors, non-viral gene delivery systems or other gene therapies achieves a transfection efficiency of the retinal and/or choroidal cells of less than 0.001%, 0.01%, 0.1%, 1%, 3%, 5%, 10%, 25%, 50%, 75% or 90%.
In some embodiments, the injection system is used to deliver a small or large molecule therapy targeted against VEGF or VEGFR, such as including, but not limited to, ziv-aflibercept, pazopanib, bevacizumab, cabozantinib, sunitinib, sorafenib, axitinib, regorafenib, ponatinib, cabozantinib, vandetanib, ramucirumab, lenvatinib, and bevacizumab.
In some embodiments, the injection system is used to deliver a gene therapy that targets, replaces, inhibits, or promotes one or more of the following genes to impart a therapeutic effect for a hereditary ocular disease or disorder including, but not limited to, MTP, HGD, SLC16A2, POLG, ALMS1, FGFR2, PRPS1, APTX, ATM, DNMT1, TGFBI, ACTB, FGFR2, BEST1, CYP4V2, NOD2, FOXL2, ABCC9, ERCC6, CYP27A1, CHS1, SH3BP2, HDAC6, CHM, SLC9A6, NSDHL, OPN1MW, OPN1LW, OPN1SW, KERA, IGBP1, OPA3, UGT1A1, FGFR2, FGFR3, ATP6V0A2, CTNS, EFEMP1, SALL4, ADAMTSL4, FBN1, ADAMTSL4, NR2E3, TGFBI, GLA, IKBKAP, LCAT, GALK1, GALT, GBA, GLB1, PORCN, TGFBI, OAT, ENG, CBS, MBTPS2, IKBKG, CNNM4, ATRX, GALC, TGFBI, HADHA, OCRL1, PLP1, B3GALTL, PAH, ARX, LOXL1, TGFBI, PQBP1, RB1, IDUA, IDS, SGSH, NAGLU, HGSNAT, GNS, GALNS, GLB1, ARSB, GUSB, FGFR3, LMX1B, NHS, STAC3, NF1, NF2, NF1, MT-ATP6, NDP, RP1L1, GPR143, PABN1, HEXB, UBIAD1, AGK, RAIL HBB, TIMP3, ATP2B3, ABCA4, ELOVL4, PROM1, GNAQ, SUOX, NAA10, BCOR, SOX2, OTX2, BMP4, HCCS, STRA6, VAX1, RARB, HMGB3, MAB21L2, RBM10, HEXA, TGFBI, SHOX, TAT, PTEN, VHL, VCAN, NF1, ZC4H2, ATP7B, CNGA3, CNGB3, JAG1, NOTCH2, PAX6, ELP4, FOXE3, PITX3, PITX2, FOXC1, CHD7, SEMA3E, ERCC6, ERCC8, CYP1B1, MYOC, MYOC, CYP1B1, FGFR1, FGFR2, FGFR1, FGFR2, NDN, SNRPN, PHYH, PEX7, CREBBP, EP300, OPA1, OPTN, SAG, GRK1, TWIST1, FGFR2, GPC3, OFD1, TSC1, TSC2, PRPH2, BEST1, WFS1, CISD2, COL4A5, COL4A4, COL4A3, UBE3A, CDKLS, MECP2, PTCH1, PTCH2, SUFU, NSD1, H19, KCNQ1OT1, CDKN1C, OPN1LW, OPN1MW, EYA1, SIX1, SIX5, KIF21A, PHOX2A, ARIX, TUBB3, SMC1A, HDAC8, COL5A1, COL5A2, COL3A1, TNXB, OPTN, ASB10, WDR36, MTND1, MTND4, MTNDS, MTND6, PAX6, PITX2, CYP1B1, FOXC1, DMPK, ZNF9, CNBP, NPC1, NPC2, SMPD1, TYR, OCA2, TYRP1, or SLC45A2, MC1R, COL1A1, COL1A2, CRTAP, LEPRE1, NPHP1, NPHP4 SDCCAG8, WDR19, CEP290, IQCB1, HESX1, OTX2, SOX2, COL2A1, COL11A1, COL11A2, COL9A1, COL9A2, MYO7A, USH2A, EDN3, EDNRB, MITF, PAX3, SNAI2, SOX10, ADAMTS10, FBN1, LTBP2, XPA, XPC, ERCC2, ERCC3, and POLH.
In some embodiments, the delivery system of the present disclosure may be used to deliver gene therapy to treat age-related macular degeneration (AMD) or diabetic macular edema (DME). In some embodiments, the delivery system of the present disclosure is used for suprachoroidal (SCS) delivery of a composition comprising a AAV vector including one or more genes to block VEGFR-2, optionally with a CAG promoter. In some embodiments, other suitable promoters include, but are not limited to, human bestrophin (hVMD2), cytomegalovirus (CMV), SV40, mGluR6, CB7, UbiC, RZ, RedO, Rho and Best1. In some embodiments, such system may include a 25-34 gauge puncture element with a polypropylene or glass syringe and fluoropolymer, silicone or rubber for the pushing sealing element stopper and floating sealing element stopper. In some embodiments, about 80-120 (for example, 100) microliters of such gene therapy composition can be delivered over 5-60 seconds. In some embodiments, the puncture element may have a bevel length less than 2 mm, less than 1 mm or less than 0.5 mm. The bevel angle can be greater than 15 degrees, greater than 30 degrees, or even greater than 45 degrees. In some embodiments, the puncture element can be 25 gauge and higher, 27 gauge and higher, or 30 gauge or higher. In some embodiments the needle has a secondary bevel to lower cutting forces.
In some embodiments, the delivery system is utilized to deliver small or large molecule injection agents such as, anti-VEGF drugs including, but not limited to, bevacizumab, ranibizumab, aflibercept, Ramucirumab, disintegrins, anti-prostaglandins, tryptophanyl-tRNA synthetase-derived polypeptides, Inosine monophosphate dehydrogenase (IMPDH) inhibitors and anti-PDGF to treat AMD; and corticosteroids to treat uveitis, chorioretinitis, or other inflammatory eye diseases; botulinum toxin for various ocular applications; tyrosine kinase inhibitors (such as Vandetanib, Axitinib, Pazopanib, Sunitinib, Sorafenib) to treat pterygium, dry eye or AMD; levo-betaxolol, or other betaadrenoceptor antagonists and 5-HT1A agonists to treat retinal pathologies.
In some embodiments, the injection system is used to deliver small molecule Wnt inhibitors to decrease angiogenesis. These small molecular Wnt inhibitors can include indazole-3-carboxamide compound or analogs thereof (WO2013040215A1), y-diketones or salts or analogs thereof (WO2014130869A1), azaindazole compound or analogs (e.g. 3-(1h-benzo[d]imidazol-2-yl)-1h-pyrazolo[3,4-c]pyridine) thereof (WO2016040180A1), N-(5-(3-(7-(3-fluorophenyl)-3H-imidazo[4,5-c]pyridin-2-yl)-1H-indazol-5-yl)pyridin-3-yl)-3-methylbutanamide, including amorphous and polymorph forms thereof (WO2017210407A1), Isoquinolin-3-yl carboxamides or salt or analogs and including amorphous and polymorph forms thereof (WO2017189823A2), Diazanaphthalen-3-yl carboxamides or salt or analogs and including amorphous and polymorph forms (US20190127370A1), 6-(5-membered heteroaryl)isoquinolin-3-yl-(5-membered heteroaryl) carboxamides or salt or analogs and including amorphous and polymorph forms (WO2019084496A1), 6-(6-membered heteroaryl & aryl)isoquinolin-3-yl carboxamides or salt or analogs and including amorphous and polymorph forms (US20190125740A1), 3-(3h-imidazo[4,5-b]pyridin-2-yl)-1h-pyrazolo[3,4-b]pyridine (US20190119303A1), Wnt inhibitors containing an indazole core or salt or analogs and including amorphous and polymorph forms (WO2013151708A1), 1h-pyrazolo[3,4-b]pyridines or salt or analogs and including amorphous and polymorph forms (WO2013166396A2), 2-(1h-indazol-3-yl)-3h-imidazo[4,5-b]pyridine or salt or analogs and including amorphous and polymorph forms (US20190055238A1), f3-diketone, y-diketone or y-hydroxyketone or salts or analogs thereof (WO2012024404A1), 3-(benzoimidazol-2-yl)-indazole inhibitors or salt or analogs and including amorphous and polymorph forms (U.S. Ser. No. 10/183,929B2), 3-(1h-imidazo[4,5-c]pyridin-2-yl)-1h-pyrazolo[3,4-b]pyridine or salt or analogs and including amorphous and polymorph forms (US20180325910A1), 1H-pyrazolo [3,4-b] pyridines or salt or analogs and including amorphous and polymorph forms (CY-1119844-T1), 3-(1h-imidazo[4,5-c]pyridin-2-yl)-1h-pyrazolo[3,4-c]pyridine or salt or analogs and including amorphous and polymorph forms (US-2018250269-A1), N-(5-(3-(7-(3-fluorophenyl)-3H-imidazo[4,5-c]pyridin-2-yl)-1H-indazol-5-yl)pyridin-3-yl)-3-methylbutanamide or salt or analogs and including amorphous and polymorph forms, (US20180133199A1), indazole-3-carboxamides or salt or analogs and including amorphous and polymorph forms (US-2018185343-A1), 3-(3h-imidazo[4,5-b]pyridin-2-yl)-1h-pyrazolo[3,4-c]pyridine or salt or analogs and including amorphous and polymorph forms (US-2018201624-A1), 2-(1h-indazol-3-yl)-1h-imidazo[4,5-c]pyridine or salt or analogs and including amorphous and polymorph forms (US-2018215753-A1), 3-(3H-imidazo[4,5-C]pyridin-2-yl)-1H-pyrazolo[3,4-C]pyridine or salt or analogs and including amorphous and polymorph forms (U.S. Ser. No. 10/052,331-B2), 5-substituted indazole-3-carboxamides or salt or analogs and including amorphous and polymorph forms (US-2018127377-A1), 3-(3H-imidazo[4,5-C]pyridin-2-yl)-1H-pyrazolo[4,3-B]pyridines or salt or analogs and including amorphous and polymorph forms (U.S. Ser. No. 10/188,634-B2), 3-(1H-imidazo[4,5-C]pyridin-2-yl)-1H-pyrazolo[4,3-B]pyridines or salt or analogs and including amorphous and polymorph forms (U.S. Ser. No. 10/195,185-B2), 3-(1h-pyrrolo[2,3-b]pyridin-2-yl)-1h-indazoles or salt or analogs and including amorphous and polymorph forms (WO-2017024021-A1), 3-(1h-pyrrolo[2,3-c]pyridin-2-yl)-1h-pyrazolo[3,4-c]pyridines or salt or analogs and including amorphous and polymorph forms (WO-2017023975-A1), 3-(1h-indol-2-yl)-1h-pyrazolo[3,4-b]pyridines or salt or analogs and including amorphous and polymorph forms (US-2018214428-A1), 3-(1h-pyrrolo[3,2-c]pyridin-2-yl)-1h-indazoles or salt or analogs and including amorphous and polymorph forms (US-2018221350-A1), 3-(1h-indol-2-yl)-1h-indazoles or salt or analogs and including amorphous and polymorph forms (WO-2017023986-A1), 3-(1H-pyrrolo[2,3-B]pyridin-2-yl)-1H-pyrazolo[4,3-B]pyridines or salt or analogs and including amorphous and polymorph forms (U.S. Ser. No. 10/206,909-B2), 3-(1h-pyrrolo[3,2-c]pyridin-2-yl)-1h-pyrazolo[4,3-b]pyridines or salt or analogs and including amorphous and polymorph forms (WO-2017024003-A1), 3-(1h-pyrrolo[3,2-c]pyridin-2-yl)-1h-pyrazolo[3,4-b]pyridines or salt or analogs and including amorphous and polymorph forms (US-2018221341-A1), 3-(3h-imidazo[4,5-b]pyridin-2-yl)-1h-pyrazolo[4,3-b]pyridines or salt or analogs and including amorphous and polymorph forms (WO-2017024015-A1), 3-(1h-pyrrolo[2,3-c]pyridin-2-yl)-1h-pyrazolo[3,4-b]pyridines or salt or analogs and including amorphous and polymorph forms (US-2018221352-A1), 3-(1H-pyrrolo[3,2-C]pyridin-2-YL)-1H-pyrazolo[3,4-C]pyridines or salt or analogs and including amorphous and polymorph forms (U.S. Ser. No. 10/206,908-B2). Each of the references referenced herein are incorporated by reference in their entirety.
In some embodiments, the injection system is utilized to deliver suspensions of injection agents including microencapsulated agents, nanoencapsulated agents, pure protein nanoparticles and poorly water-soluble or water-insoluble agents.
In some embodiments, the injection agent or encapsulated injection agent is delivered with a residence time extending matrix. The matrix can consist of reverse thermally responsive hydrogels, self-assembling hydrogels, bioadhesive polymer networks, hydrogels, fibronectin-containing hydrogels, enzyme-responsive hydrogels, ultrasound sensitive hydrogels, pH-sensitive hydrogels, carbohydrates, two or more component hydrogels, and multi-component double network hydrogels.
In some embodiments, the injection agent is delivered via the injection system with following a permeation enhancer such as including, but not limited to, dimethylsulfoxide (DMSO), collagenases, elastases, proteases, papain, bromelain, peptidases, lipases, alcohols, polyols, short chain glycerides, amines, amides, cyclodextrins, fatty acids, pyrrolidones, Cyclopentadecalactone, Sodium N-[8-(2-hydroxylbenzoyl)amino] caprylate (SNAC), 8-(N-2-hydroxy-5-chloro-benzoyl)-amino-caprylic acid (5-CNAC), Sodium caprate, Sodium caprylate, omega 3 fatty acid, protease inhibitors, alkylglycosides, chitosan, Dodecyl-2-N,N-dimethylamino propionate (DDAIP), N-methyl-2-pyrrolidone (NMP), azones, sulfoxides, surfactants, benzylalkonium choride, saponin, bile salts, bile acids, cell penetrating peptides, polyarginine, low molecular weight protamine, polyserine, capric acid, gelucires, semifluorinated alkanes, terpenes, phospholipids, chelators, Ethylenediamine Tetraacetic acid (EDTA), citrate, crown ethers and combinations thereof.
In some embodiments, the injection agent having one or more therapeutic formulations is delivered via the injection system with or following administration of one or more vasoconstrictive agents to reduce efflux of the injection agent via the choroidal blood vessels, including, but not limited to 25I-NBOMe, Amphetamines, AMT, Antihistamines, Caffeine, Cocaine, Dopamine, Dobutamine, DOM, LSA, LSD, Methylphenidate, Mephedrone, Norepinephrine, Oxymetazoline, Phenylephrine, Propylhexedrine, Pseudoephedrine, Stimulants, Serotonin 5-hydroxytryptamine agonists, triptans and Tetrahydrozoline hydrochloride. In some embodiments, these agents may be administered using the injection system of the present disclosure into the SCS or via an intravitreal injection using a standard syringe. The vasoconstrictive agents can be delivered before, simultaneously, or after the administration of the one or more therapeutic formulations.
In some embodiments, the injection agent delivered via the injection system achieves SCS coverage in excess of 20%, 40%, 60% or 80%.
In some embodiments, the injection agent delivered via the injection system with or without one or more vasoconstrictive agents to reduce efflux of the injection agent via the choroidal blood vessels achieves SCS coverage in less than 180, 120, 60, 30 or 15 minutes.
In some embodiments, the injection agent delivered via the injection system has a retention time within the SCS of less than 180, 120, 60, 30, 15, 10 or 5 minutes.
In some embodiments, the injection agent is delivered via the injection system in less than 500, 400, 300, 200 or 100 microliters.
In some embodiments, the injection agent is delivered via the injection system in concentrations less than 80%, 60%, 40% 20%, 10%, 5%, 2.5% or 1%.
In some embodiments, the percent dosage of the injection agent delivered via the injection system delivered to the subretinal space is less than 80%, 60%, 40% 20%, 10%, 5%, 2.5% or 1%.
In some embodiments, the injection agent delivered via the injection system is dosed at least once every 10 years, once every 5 years, once every 2 years, once every 1 year, once every 6 months, once every 3 months, once a month or once a week.
In some embodiments, the injection system is used to deliver one or multiple injection agents to treat one or more of the ocular causes or effects of the following diseases including, but not limited to, Abetalipoproteinemia (Bassen-Kornzweig Syndrome), Alkaptonuria, Allan-Herndon-Dudley Syndrome, Alpers Syndrome, Alstrom Syndrome, Apert Syndrome, Arts Syndrome (Mental Retardation, X-Linked, Syndromic 18), Ataxia-Oculomotor Apraxia Syndrome, Ataxia Telangiectasia (Louis-Bar Syndrome), Autosomal Dominant Cerebellar Ataxia Deafness and Narcolepsy (ADCADN), Avellino Corneal Dystrophy (Combined Granular-Lattice Corneal Dystrophy), Baraitser-Winter Syndrome 1, Beare-Stevenson Syndrome, Best Macular Dystrophy, Bietti Crystalline Corneoretinal Dystrophy, Blau Syndrome, Blepharophimosis, Ptosis, and Epicanthus Inversus (BPES), Cantu Syndrome, Cerebrooculofacioskeletal Syndrome, Cerebrotendinous Xanthomatosis, Chediak-Higashi Syndrome, Cherubism, Chondrodysplasia with Platyspondyly, Distinctive Brachydactyly, Hydrocephaly, and Microphthalmia, Choroideremia, Christianson Syndrome, CK Syndrome, Colorblindness, Deutan, Colorblindness, Protan, Colorblindness, Tritanopic, Cornea Plana, Corpus Callosum, Agenesis of, with Mental Retardation, Ocular Coloboma, and Micrognathia, Costeff Syndrome, Crigler-Najjar, Crouzon Syndrome, Crouzon Syndrome with Acanthosis Nigricans (Crouzonodermoskeletal Syndrome), Cutis Laxa, Debre Type, Cystinosis, Doyne Honeycomb Dystrophy (Malattia Leventinese), Duane-Radial Ray Syndrome, Ectopia Lentis et Pupillae, Ectopia Lentis, Familial, Ectopia Lentis, Isolated, Enhanced S-Cone Syndrome, Epithelia Basement Membrane Corneal, Dystrophy (Map-Dot-Fingerprint Corneal Dystrophy), Fabry Disease (Hereditary, Dystopic Lipidosis), Familial Dysautonomia, Fish-Eye Disease, Galactokinase Deficiency, Galactosemia, Gaucher's Disease, GM1-Gangliosidosis, Type I, GM1-Gangliosidosis, Type II, GM1-Gangliosidosis, Type III, Goltz Syndrome, Granular, Corneal Dystrophy (Groenouw Type I), Gyrate Atrophy, Hereditary Hemorrhagic Telangietasia (Osler-Rendu-Weber Disease), Homocystinuria, IFAP Syndrome with or without Bresheck Syndrome, Incontinentia Pigmenti (Bloch-Sulzberger Syndrome), Jalili Syndrome, Juberg-Marsidi Syndrome, Krabbe Disease, Lattice Corneal Dystrophy, LCHAD (Long-Chain 3-Hydroxyacyl-Coa Dehydrogenase) Deficiency, Lowe, Pelizaeus-Merzbacher, Peters-Plus Syndrome (Krause-Kivlin Syndrome), Phenylketonuria, Proud Syndrome, Pseudoexfoliation Syndrome, Reis-Bucklers Corneal Dystrophy, Renpenning Syndrome (Mental Retardation, X-Linked, Renpenning Type), Retinoblastoma, Retinoschisis, Juvenile X Linked, Russell-Silver Syndrome, Mucopolysaccharidosis Type IH (Hurler Syndrome), Mucopolysaccharidosis Type IH/S (Hurler-Scheie Syndrome), Mucopolysaccharidosis Type IS (Scheie Syndrome), Mucopolysaccharidosis Type II (Hunter Syndrome), Mucopolysaccharidosis Type IIIA (Sanfilippo Syndrome A), Mucopolysaccharidosis Type IIIB (Sanfilippo Syndrome B), Mucopolysaccharidosis Type IIIC (Sanfilippo Syndrome C), Mucopolysaccharidosis Type IIID (Sanfilippo Syndrome D), Mucopolysaccharidosis Type IVA (Morquio Syndrome A), Mucopolysaccharidosis Type IVB (Morquio Syndrome B), Mucopolysaccharidosis Type VI (Maroteaux-Lamy Syndrome), Mucopolysaccharidosis Type VII (Sly Syndrome), Muenke Syndrome, Nail-Patella Syndrome, Nance-Horan Syndrome Native American Myopathy, Neurofibromatosis Type I, Neurofibromatosis Type II, Neurofibromatosis-Noonan Syndrome, Neuropathy, Ataxia, and Retinitis, Pigmentosa (NARP), Norrie Disease, Occult Macular Dystrophy, Ocular Albinism, Oculopharyngeal Muscular Dystrophy, Sandhoff Disease (GM2-Gangliosidosis, Type II), Schnyder Corneal Dystrophy, Sengers Syndrome, Smith-Magenis Syndrome, (Chromosome 17p11.2 Deletion Syndrome), Sickle Cell Anemia, Sorsby Fundus Dystrophy, Spinocerebellar Ataxia, X-Linked 1, Stargardt Disease/Fundus, Flavimaculatus, Sturge-Weber Syndrome, Sulfocysteinuria (Sulfite Oxidase Deficiency), Syndromic Microphthalmia 1 (Lenz Microphthalmia Syndrome), Syndromic Microphthalmia 2 (Oculofaciocardiodental Syndrome), Syndromic, Microphthalmia 3 (Microphthalmia and Esophageal Atresia Syndrome), Syndromic Microphthalmia 5, Syndromic Microphthalmia 6, Syndromic Microphthalmia 7, (Midas Syndrome), Syndromic Microphthalmia 9 (Matthew-Wood Syndrome), Syndromic Microphthalmia 11, Syndromic Microphthalmia 12, Syndromic Microphthalmia 13, Syndromic Microphthalmia 14, Tarp Syndrome, Tay-Sachs Disease (GM2-Gangliosidosis, Type I), Thiel-Behnke Corneal Dystrophy, Turner Syndrome, Tyrosinemia, Type II, Vacterl Association with Hydrocephalus, Von Hippel-Lindau Syndrome, Wagner Syndrome, Watson Syndrome, Wieacker-Wolff Syndrome, Wilson Disease, Achromatopsia, Alagille Syndrome, Aniridia, Anterior Segment Mesenchymal Dysgenesis, Axenfeld-Rieger Syndrome, Charge Syndrome, Cockayne Syndrome, Glaucoma, Congenital, Glaucoma, Open Angle Juvenile Onset, Jackson-Weiss Syndrome, Pfeiffer Syndrome, Prader-Willi Syndrome, Ref Sum Disease, Rubinstein-Taybi Syndrome, Normal-Tension Glaucoma, Oguchi Disease, Saethre-Chotzen Syndrome, Simpson-Golabi-Behmel Syndrome, Tuberous Sclerosis, Vitelliform Macular Dystrophy, Adult-Onset, Wolfram Syndrome, Alport Syndrome, Angelman Syndrome, Bardet Biedl Syndrome, Basal Cell Nevus Syndrome, Beckwith-Wiedemann Syndrome, Blue-Cone Monochromacy, Branchiootorenal Syndrome, Charcot-Marie-Tooth Disease, Cone-Rod Dystrophy, Congenital Disorder of Glycosylation, Congential Fibrosis of Extraocular Muscles, Congenital Nystagmus, Congenital Stationary Night Blindness, Cornelia de Lange Syndrome, Dyskeratosis Congenita, Ehlers-Danlos Syndrome, Fuch's Endothelial Corneal Dystrophy, Glaucoma, Open Angle Adult Onset, Hermansy-Pudlak Syndrome, Joubert Syndrome, Kearns-Sayre Syndrome, Leber Congenital Amaurosis, Leber Hereditary Optic Neuropathy, Leigh Syndrome, Peters' Anomaly Retinitis Pigmentosa, Muscular Dystrophy-Dystroglycanopathy, Myotonic Dystrophy, Niemann-Pick Disease, Noonan Syndrome, Neuronal Ceroid Lipofuscinosis, Oculocutaneous Albinism, Optic Atrophy, Oral-Facial-Digital Syndrome, Osteogenesis Imperfecta, Senior-Loken Syndrome, Septic-Optic Dysplasia (de Morsier Syndrome), Spastic Paraplegia, Stickler Syndrome, Treacher Collins Syndrome, Usher Syndrome, Waardenburg Syndrome, Weill-Marchesani Syndrome, and Xeroderma Pigmentosum.
In some embodiments, multiple injections may be performed over time to allow continuation of therapy. The injection of therapeutic may be accompanied by another agent that enables multiple deliveries. For e.g. AAV delivery is limited by immune response to AAV which usually limits the AAV usage to a single time treatment, a limitation commonly associated with intravitreal injection, and while sub-retinal injection is immune privileged, the damaged and diseased retina does not tolerate multiple injections without trauma. Another agent (such as ImmTOR) that suppresses this response can be injected prior, in combination, or after the AAV injection to mitigate the immune response and enable AAV therapy at multiple time points. This allows one to titrate the dose to patient response as necessary.
In some embodiments, the route of administration is by injection into the SCS. In some embodiments, the genetic disease or disorder is diagnosed by gene sequencing such as including, but not limited to, Sanger sequencing, next generation sequencing, high-throughput screening, exome sequencing, Maxam-Gilbert sequencing, chain-termination methods, shotgun sequencing, Bridge polymerase chain reaction, single molecule real-time sequencing, ion torrent sequencing, pyrosequencing, sequencing by synthesis, combinatorial probe anchor synthesis, sequencing by ligation and nanopore sequencing. In some embodiments, the ocular disease or disorder is diagnosed by an eye exam, an ophthalmoscope, ocular coherence tomography, retinal scanning, fluorescein staining, conjunctival staining, color vision testing, optic disc imaging, nerve fiber layer analysis, corneal topography, electro-diagnostic testing, fluorescein angiography, photography of the eye, specular microscopy, visual field testing, ultrasound of the eye and combinations thereof.
In some embodiments, a patient presents with elevated intraocular pressure and is diagnosed with early stage juvenile primary open angle glaucoma before significant optic nerve damage has occurred after being examined with an ophthalmoscope. A blood sample is drawn and sent for genetic testing, which determines that the patient has a mutation in the olfactomedin domain of his myocilin (MYOC) gene, mutation Y437H, that is likely implicated in causing the disease, leading to a diagnosis of myocilin-associated primary open angle glaucoma.
The patient is then treated by dosing with the injection system, administering microRNA complementary to the first 22 bases of mRNA for the MYOC gene formulated in aqueous solution of a self-assembling hydrogel with betacyclodextrin and EDTA as permeation enhancers. Prior to use, the injection is stored as a lyophilized powder in separate vials from the diluent. Following injection, the hydrogel self-assembles in the SCS after delivery providing sustained delivery of the microRNA that suppresses myocilin expression, leading to a reduced accumulation of myocilin in the trabecular meshwork, resulting in reduced intraocular pressure, thereby reducing the probability of sustaining optic nerve damage for the patient.
In another specific embodiment, a male child presents with night blindness and on exam is found to have reduced visual field and some retinal degeneration. A blood sample is drawn and sent for genetic testing, which determines that the patient has a mutation in his CHM gene, containing part or the entirety of the CHM gene sequence as described, for example, in https://www.uniprot.org/uniprot/P24386, incorporated herein by reference in its entirety, which encodes RAB escort protein 1 (REP1), which supports a diagnosis of early stage choroideremia.
The patient is then treated by dosing with the injection system, in which lyophilized AAV2 vector containing a retinal specific promoter, derived from the rhodopsin kinase (RK) promoter gene expressed in rods and cones, connected to the human CHM gene, has been reconstituted with its aqueous diluent prior to injection. On reconstitution, the injection agent solution contains approximately 1013 AAV vectors per milliliter. Once injected, the RK promoter and human CHM gene will be stably transfected into photoreceptor cells, where the corrected form of REP 1 will be expressed, treating the patient's choroideremia.
In another specific embodiment, an elderly patient presents with central vision defects. On routine retinal examination, drusen are detected. Fluorescein angiography demonstrates leaky choroidal vasculature, confirmed by the presence of sub-retinal fluid accumulation observed on optical coherence tomography (OCT). The patient is diagnosed with early stage neovascular age-related macular degeneration (AMD).
The patient is then treated by dosing with the injection system, in which 21-24 nucleotide short interfering RNA (siRNA) sequences complementary to portions the mRNA of one or more of the following alone or in combination of, vascular endothelial growth factor (VEGF), any of its sub-types including, but not limited to VEGF-A, VEGF-A121, VEGF-A165, VEGF-A189, VEGF-A206 VEGF-B, VEGF-C, VEGF-D, VEGF receptors (VEGFRs), VEGFR-1, VEGFR-2, VEGFR-3, NOTCH regulated ankyrin repeat protein (NRARP), and other angiogenesis promoting proteins encoding genes. The siRNA is delivered in a suspension of liposomal carriers. Following delivery, the siRNA knocks down expression of the angiogenesis promoting protein or proteins thereby preventing additional choroidal capillary growth and causing capillary regression yielding reduced choroidal capillary retinal and macular invasion and improved central vision. In a specific embodiment, the siRNA is targeted to knock down VEGFR-2, which has a gene sequence or isoforms thereof as described in https://www.uniprot.org/uniport/P35968, incorporated herein in its entirety.
In another specific embodiment, a patient diagnosed with neovascular AMD or diabetic retinopathy is treated by dosing with the injection system, in which an AAV vector, or other transfection vector, contains a gene that when transcribed produces an RNA sequence that is complementary to at least a portion of the mRNA that is translated into VEGFR-2. In delivering this gene therapy to the SCS, the choroidal capillaries, also referred to as choriocapillaris, contact the delivered therapeutic targeted at transfecting those cells expressing VEGFR-2. On transfection, the siRNA or shRNA vectors that are transcribed knock down or knock out VEGFR-2 production thereby reducing neovascularization to treat AMD or diabetic retinopathy.
In some embodiments, the physician may be presented with a suprachoroidal injection assembly or kit, which includes (1) a volume of the injection agent comprising one or more therapeutic agent formulations, i.e. active agent formulations, for example, containing an effective amount of an agent useful for treating a condition of an eye of a patient; (2) an injection system as described above and (3) optionally, an injector to facilitate ejection of the injection agent into and through the injection system membrane.
As described earlier, the agent formulation can comprise of various forms, such as solutions and suspensions of various viscosity. The entire kit is sterile including the formulation, injection system, and facilitating injector.
In some embodiments, the total volume of the active agent formulation to be injected in the suprachoroidal space is preferably in the range of approximately 0.01-0.5 mL. In some embodiments, the active agent may be provided in a lyophilized form and an accompanying diluent to create the suspension at the time of injection. In some embodiments, the active agent may be premixed. In some embodiments, the injection system may be prefilled with premixed formulation. In some embodiments, the user may fill the injection system immediately prior to administering the therapeutic formulation to the patient. In some embodiments, the injection system may contain multiple chambers with frangible separation. In some embodiments, the puncture element has initial penetrating length of 0.01 to 3 mm and the puncture element extends further while performing injection. In some embodiments, the injection system and injection facilitator can be preassembled with prefilled formulation and ready for use without any further assembly. In some embodiments, entire kit is packaged in a single pouch/tray to maintain sterility. In some embodiments, where components are packaged separately or in a combination. In some embodiments, the kit is sterilized together or separately by one of the sterilization methods including but not limited to autoclave, ethylene oxide, gamma radiation etc.
In some embodiments, where the components are present in a secondary package. In some embodiments, the kit is stored as a set at low enough temperature to extend the life of the active pharmaceutical agent. In some embodiments, the formulation is stored at low temperature separately while the rest of kit is stored at room temperature.
Computer Systems for Use with the Injection Systems
The systems of the present disclosure can include a controller for controlling the operation of the injection systems of the present disclosure. In some embodiments, such controller may be a computer system to collect and analyze the sensor information used by the system to control the injection assembly. Any suitable computing systems can be used to implement the computing devices and methods/functionality described herein and be converted to a specific system for performing the operations and features described herein through modification of hardware, software, and firmware, in a manner significantly more than mere execution of software on a generic computing device, as would be appreciated by those of skill in the art. One illustrative example of such a computing device 1900 is depicted in
The computing device 1900 can include a bus 1910 that can be coupled to one or more of the following illustrative components, directly or indirectly: a memory 1912, one or more processors 1914, one or more presentation components 1916, input/output ports 1918, input/output components 1920, and a power supply 1924. One of skill in the art will appreciate that the bus 1910 can include one or more busses, such as an address bus, a data bus, or any combination thereof. One of skill in the art additionally will appreciate that, depending on the intended applications and uses of a particular embodiment, multiple of these components can be implemented by a single device. Similarly, in some instances, a single component can be implemented by multiple devices. As such,
The computing device 1900 can include or interact with a variety of computer-readable media. For example, computer-readable media can include Random Access Memory (RAM); Read Only Memory (ROM); Electronically Erasable Programmable Read Only Memory (EEPROM); flash memory or other memory technologies; CDROM, digital versatile disks (DVD) or other optical or holographic media; magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices that can be used to encode information and can be accessed by the computing device 1900.
The memory 1912 can include computer-storage media in the form of volatile and/or nonvolatile memory. The memory 1912 may be removable, non-removable, or any combination thereof. Exemplary hardware devices are devices such as hard drives, solid-state memory, optical-disc drives, and the like. The computing device 1900 can include one or more processors that read data from components such as the memory 1912, the various I/O components 1920, etc. Presentation component(s) 1916 present data indications to a user or other device. Exemplary presentation components include a display device, speaker, printing component, vibrating component, etc.
The I/O ports 1918 can enable the computing device 1900 to be logically coupled to other devices, such as I/O components 1920. Some of the I/O components 1920 can be built into the computing device 1900. Examples of such I/O components 1920 include a microphone, joystick, recording device, game pad, satellite dish, scanner, printer, wireless device, networking device, and the like.
Various modifications and alternative embodiments of the present invention will be apparent to those skilled in the art in view of the foregoing description. Accordingly, this description is to be construed as illustrative only and is for the purpose of teaching those skilled in the art the best mode for carrying out the present invention. Details of the structure may vary substantially without departing from the spirit of the present invention, and exclusive use of all modifications that come within the scope of the appended claims is reserved. Within this specification embodiments have been described in a way which enables a clear and concise specification to be written, but it is intended and will be appreciated that embodiments may be variously combined or separated without parting from the invention. It is intended that the present invention be limited only to the extent required by the appended claims and the applicable rules of law.
It is also to be understood that the following claims are to cover all generic and specific features of the invention described herein, and all statements of the scope of the invention which, as a matter of language, might be said to fall therebetween.
This application claims the benefit of and priority to U.S. Provisional Application Ser. No. 63/064,975, filed on Aug. 13, 2020, which is incorporated herein by reference in its entirety.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2021/046001 | 8/13/2021 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 63064975 | Aug 2020 | US |
