JP2024513779A - Modulated power injector with input device - Google Patents

Abstract

A system for injecting a medium into a patient includes an automatic injector having a reservoir, an ejector for expelling a quantity of fluid medium from the reservoir, and an actuator coupled to the ejector. An input device includes a syringe housing, a plunger, a circuit board coupled to a first component of the input device, a plunger position sensor, a battery, and a transmitter for transmitting an input device operating signal to the automatic injector. The input device operating signal is based at least in part on the signal transmitted from the plunger position sensor. A flow diverter is disposed downstream of the reservoir and configured to receive at least a first portion of the quantity of fluid medium expelled from the reservoir. (FIG. 1)

Description

Cross-references to related applications This application was filed as a PCT patent international application on January 10, 2022, and was filed on March 26, 2021 for “MODULATED POWER INJECTOR WITH INPUT SYRINGE”. 63/166,679, entitled U.S. Provisional Patent Application No. 63/166,679. The disclosure of this US provisional patent application is incorporated herein by reference in its entirety. This application is also filed in U.S. Patent Application Publication No. 16/931 entitled "SYSTEMS AND METHODS FOR MEASURING INJECTED FLUIDS," filed on July 17, 2020. , 664, which is a continuation-in-part of U.S. Patent Application Publication No. 62/875,859, filed on July 18, 2019. The disclosure of this US provisional patent application is incorporated herein by reference in its entirety.

Power injectors may be used to inject drugs, saline, contrast agents, or other drugs or fluids into patients undergoing medical procedures. Typically, the autoinjector is controlled by pressing a control button on the autoinjector.

In one aspect, the present technology relates to a system for injecting a medium into a patient. The system includes an autoinjector, the autoinjector comprising a media tank, an ejector for ejecting a quantity of fluid media from the media tank, and an actuator coupled to the ejector; an input device communicatively coupled to the actuator, the input device coupled to a syringe housing, a plunger slidably received within the syringe housing, and a first component of the input device. a circuit board, a plunger position sensor, a battery coupled to the circuit board and configured to power the plunger position sensor, and an input device coupled to the circuit board for transmitting an operating signal to the autoinjector. a transmitter, wherein the input device operating signal is based at least in part on a signal transmitted from a plunger position sensor; The apparatus includes a flow diverter configured to receive at least a first portion of a quantity of fluid medium discharged from a media tank. In one example, the transmitter includes a wireless transmitter and the autoinjector includes a wireless receiver for receiving the input device operation signal. In another example, the input device further includes a spring for biasing the plunger against the syringe housing. In yet another example, the media tank includes a syringe barrel, the ejector includes a plunger slidably disposed within the syringe barrel, and the actuator includes a lead screw and a motor coupled to the lead screw. , rotation of the lead screw advances the ejector within the syringe barrel. In yet another example, the autoinjector further includes a position sensor for detecting the position of the ejector and/or the lead screw.

Another example of the above embodiment further comprises a patient connection element downstream of the flow diversion device for receiving at least a second portion of the quantity of fluid medium discharged from the medium tank. In one example, the first portion of the volume of fluid medium and the second portion of the volume of fluid medium are comprised of the volume of fluid medium discharged from the media tank. In another example, the flow diversion device includes a waste container for receiving at least a portion of the first portion of the quantity of fluid medium. In yet another example, the plunger position sensor comprises at least one Hall effect sensor coupled to the first component and a magnet coupled to the second component of the input device, the plunger position sensor comprising: is movable relative to the second component. In yet another example, the plunger position sensor includes at least one of a light emitter, a light receiver, a potentiometer, and a magnet.

In another aspect, the technology relates to a system for injecting a medium into a patient. The system includes an autoinjector comprising a media tank, an ejector for ejecting a quantity of fluid medium from the media tank, and an actuator coupled to the ejector. an infusion sensor disposed proximate the outlet; and an input device remote from and communicatively coupled to the actuator, the input device comprising: a syringe housing; and an input device slidably received within the syringe housing. a plunger, a circuit board coupled to the first component of the input device, a plunger position sensor, a battery coupled to the circuit board and configured to power the plunger position sensor, and an input device operating signal. a transmitter coupled to a circuit board for transmitting a signal to an autoinjector, the input device operation signal being based at least in part on a signal transmitted from a plunger position sensor; an input device and a memory storing instructions, the instructions, when executed by the processor, causing the autoinjector to perform an operation, the operation causing the ejector to perform an operation based at least in part on the input device operation signal. controlling the actuator to advance at a first speed; and based at least in part on the injection pressure signal received from the injection sensor, to advance the ejector at a second speed that is different than the first speed. controlling the actuator; and a memory. In one example, the processor and memory are located on the autoinjector. In another example, the position sensor comprises at least one of a Hall effect sensor, a light emitter, a light receiver, a potentiometer, and a magnet. In yet another example, controlling the actuator to advance the ejector at the second speed includes determining a target flow rate of the fluid medium proximate the injection sensor and maintaining the target flow rate for a predetermined period of time. where the predetermined time is measured from the time at which the target flow rate was determined or a variable time as a function of the input device. In yet another example, the target flow rate is determined based at least in part on an injection pressure signal transmitted from an injection sensor.

In another example of the above aspect, the target flow rate is determined based at least in part on a signal transmitted from the flow sensor.

In another aspect, the technology relates to a method of controlling the injection of a medium into a patient using an automatic injector. The method includes the steps of: receiving an input device actuation signal from an input device remote from the autoinjector; processing the input device actuation signal to obtain a first actuation signal; the first actuation signal actuating the actuator to eject the medium from the autoinjector at the first rate; and receiving the change signal from at least one of the input device and the sensor. processing the modified signal to obtain a second actuation signal; and transmitting the second actuation signal based at least in part on the modified signal. In one example, the sensor is located remotely from the autoinjector. In another example, a sensor senses pressure within a media delivery system fluidly coupled to an autoinjector and a patient. In yet another example, the sensor is disposed within the autoinjector and senses the pressure of the media within the autoinjector's media tank.

FIG. 1 shows a power injector system that includes an automatic power injector that can be activated by a hand-held input device.

FIG. 2A shows a perspective view of one embodiment of a handheld input device that utilizes a measurement sensor module.

FIG. 2B illustrates a partial perspective cross-sectional view of the input device of FIG. 2A showing a measurement sensor module including a Hall effect sensor module.

FIG. 2C shows a partially exploded perspective view of the input device of FIG. 2B.

FIG. 3 shows a perspective view of another example of an input device that utilizes a Hall effect sensor module.

FIG. 4 illustrates a system that utilizes an automatic power injector having a screw drive motor mechanism that receives, processes, and operates a motor that drives a piston and plunger in accordance with input from a hand-held input device.

FIG. 5 shows a system having an automatic power injector, a flow diversion device, a collection tank, and a sensor for measuring the medium injected from the injector and the medium diverted to the collection tank.

Figure 6 shows "Comparison of Contrast Injection Pressure Contours with Different Methods for Coronary Angiography." )”, SCAI 2020 Scientific Session, May 14-16, 2020 We present some graphical results from the abstract of the day. The abstract disclosure is incorporated herein by reference in its entirety.

FIG. 7 graphically depicts the injection profile of the medium delivered to the patient, identifying volumetric regions of "under-infusion" and "over-infusion" of the medium for opacification purposes. FIG. 7A graphically illustrates a pulsatile media injection profile of media into a patient.

FIG. 8A shows an exemplary injection profile as delivered to a patient. FIG. 8B shows an exemplary injection profile as delivered to a patient. FIG. 9A shows an exemplary injection profile as delivered to a patient. FIG. 9B shows an exemplary injection profile as delivered to a patient. FIG. 10 shows an exemplary injection profile as delivered to a patient.

FIG. 11 illustrates an example of a suitable operating environment in which one or more of the examples may be implemented.

FIG. 12 shows a method of controlling the evacuation of media from an autoinjector.

FIG. 13 shows a method of controlling the evacuation of media from an autoinjector.

The present disclosure describes systems, devices, and methods used to control, transform, or modulate the delivery of substances, such as radiopaque contrast agents, to a delivery site and/or media delivered to a delivery site. Systems, devices and methods that can be used to measure or otherwise quantitatively assess. More specifically, the purpose of the following systems, devices, and methods is to modulate and/or assess the delivery of media to blood vessels, vascular beds, organs, and/or other body structures, and to The aim is to optimize delivery of the medium to the intended site while reducing inadvertent or excessive introduction of the medium into other blood vessels, vascular beds, organs and/or other structures, including the introduction of the medium.

Terms such as vehicle(s), agent, substance, material, drug, etc. describe various fluid materials that may at least partially contain substances used in the performance of diagnostic, therapeutic and/or preventive medical treatments. as generally used herein and such usage is not intended to be limiting.

Some of the systems, devices, and methods described herein include devices and methods for optimizing delivery of media to the intended site while reducing inadvertent and/or excessive introduction of media. , may be used in conjunction with an injection system that may be automated with respect to input.

The techniques described herein are related to those presented in US Patent Application Publication No. 2021/0018348 (“Systems and Methods for Measuring Injected Fluids”). The disclosure of this US patent application publication is incorporated herein by reference in its entirety. U.S. Patent Application Publication No. 2021/0018348 discloses systems, devices, and methods for adjusting and/or modifying injections from an autoinjector. Here, the medium injected by the syringe passes through a diversion path located at the fluidic connection between the syringe and the catheter that is utilized to deliver the medium to the injection site within the patient's body. The diversion path functions to divert a portion of the injection into the patient, optimizing the injection for visualization (ie, angiography) while reducing unnecessary contrast agent being injected into the body.

In medical diagnostic, prophylactic and therapeutic practice, there are many occasions when it is preferable to deliver a drug, drug or vehicle to a specific site within the body, as opposed to a more general systemic introduction. One such exemplary opportunity involves the delivery of contrast agents to the coronary vasculature in the diagnosis (i.e., angiography) and treatment (e.g., balloon angioplasty and stenting) of coronary vascular disease. Can be mentioned. In addition to the description herein, devices and methods may be used to modulate (or otherwise alter or modulate) vehicle delivery to the coronary vasculature in the prevention of toxic systemic effects of such agents. It may be used for monitoring/measuring and/or monitoring/measuring. However, those skilled in the art will appreciate that controlled delivery and/or quantitative evaluation of media to specific vessels, structures, organs or regions of the body may also benefit from the devices and methods disclosed herein. It will be appreciated that there are many other uses. For the sake of brevity, such devices and methods may be described as related to regulating and/or measuring contrast agent delivery. Therefore, while such devices and methods may be used in the prevention of contrast agent-induced nephropathy, they are not intended to, and are not intended to, limit their use to this sole purpose. Nor should it be interpreted. Other exemplary uses include cancer therapeutics for tumors, thrombolytic agents for occluded arteries, occlusive or sclerosing agents for vascular malformations or diseased tissues, muscle beds, neural cavities or Delivery, injection, preparation or measurement of genetic material to organs, emulsions to the eye, bulking agents to muscle tissue and/or sphincters, contrast agents to the lymphatic system, antibiotics to infected tissues, supplements for kidney dialysis, etc. can be mentioned.

There are various types of automatic power devices or automatic power injectors (APIs) for injecting media into a patient. Such devices may be used in place of injection of media with a hand-held syringe. The API may be defined by its intended use and the type of media it can automatically inject, such as an MRI, CT or angiography injector. Each type of API has different usage requirements and may deliver different media depending on the device. Type of drug injected and vehicle The site at which the drug is delivered depends on the type of access (where in the body the catheter or needle is inserted), the site at which the vehicle is delivered, and any delivery device requirements that may be required. (ie, size of conduit, pressure of delivery, etc.). These are just some of the considerations when using various power injectors. Given the drug/vehicle and delivery requirements, automatic power injectors may have a variety of mechanisms for driving the fluid medium. Some examples include piston or plunger pumps, diaphragm pumps, gear pumps, centrifugal pumps, hydraulic pumps, gear pumps, screw pumps, etc., to name a few.

FIG. 1 shows a power injector system 100 that includes an automatic power injector (API) 102 that can be activated by a hand-held input device 104. API 102 is shown for powered injection of media, which may be used, for example, to inject media during angiography. As can be seen, the syringe 104 is in the form of a hand-held syringe body 106 that controls the advancement/injection of the medium into the patient. Many components located within the illustrated elements are not shown but may be shown in other figures of this application or would be obvious to one skilled in the art.

The API 102 of FIG. 1 may include a housing 108 containing an internal drive motor (not shown) and a data display 110 (indicating the status/operating parameters of the API 102). An API syringe 112, including an API barrel 114 and a plunger 116, may be attached to the API 102 to interact with an internal drive mechanism/motor (not shown). The plunger 116 may, for example, be connected to a piston further coupled to a motor-driven screw (not shown) such that the motor moves the API plunger 116 along the API barrel 114 to remove the contents of the syringe 112. Objects may be expelled (or fluid may be drawn into the interior) through the body outlet 118.

1 shows an input device 104 configured as a hand-held syringe 106 and a conduit 120 connecting an outlet 122 of the hand-held syringe 106 to an API 102, typically a port 124 on a housing 108. Input signals received from the syringe 106 may be delivered to a processor/circuit board (not shown), which may then direct/control an actuator (not shown) in the API 102 to control the movement of a motor-driven screw (not shown) to drive a piston/plunger 116 into the API barrel 114.

The input device 104 of FIG. 1 may detect the position of the plunger 126 relative to the input barrel 128. Structures utilized for this detection include, but are not limited to, one or more magnets and a sensing system that may include a potentiometer, an optical sensor, and a Hall effect sensor (to name a few). but not limited to. Such a device with detection functionality may be advantageously used as input device 104 shown in FIG. 1 to provide input to API 102. Input device 104 may be configured to mimic (in terms of feel and performance) a hand-held injection syringe often used for direct injection of contrast media. In this case, the input device 104 (discussed further herein) may prefer the performance advantages provided by the API 102, but may have more experience with the look and feel of a handheld injection device. may be readily accepted by providers, including sexual surgeons. Another advantage of untethered (i.e., wireless) handheld input devices (such as 402 in FIG. 4) includes Bluetooth, IR, RF, Wi-Fi, or other wireless communication protocols and An advantage is that it can be used in a sterile field without being tethered to API 102 because it can communicate with API 102 via a device (eg, instead of being tethered by conduit 120 as shown in FIG. 1). Such a handheld input device 104 may be disposable and does not need to be re-sterilized for different patients. These are just some of the benefits of using handheld input device 104 as an input to API 102.

FIG. 2A shows a perspective view of one embodiment of a hand-held syringe input device 200 that utilizes a Hall effect sensor module, and is described in further detail below. The input device 200 looks substantially similar to known syringes, is configured to function in substantially the same manner, and looks and feels substantially the same during use. Device 200 includes a syringe housing 202 defining an inner bore 204 . A plunger or piston, described in further detail below, is slidably received within bore 204. More specifically, the piston slidably engages the inner surface of the bore 204, and linear movement M of the plunger shaft within the bore 204 causes movement of the piston. Movement M is carried out along the syringe axis As. As discussed in more detail below, a thumb ring (or palm plunger or similar attachment element) 212 may be utilized to push and pull the plunger along axis As. The outlet end 214a may be occluded and/or sealed such that the syringe functions as a virtual input rather than actually delivering fluid medium from the outlet end 214a. Alternatively, a spring or similar resilient element may be positioned within the bore between plunger 210 (FIG. 2B) and discharge end 214a to provide tactile feedback to the physician. As the plunger moves in direction M toward the discharge end 214 of the syringe housing 202, a wireless/wired signal may be transmitted to the receiver (e.g., as shown in FIG. 4), which transmits the information to the processor/circuit board. (Figure 4). The processor may be integrated with the API or may be a standalone device. In one aspect, the data signal may be transmitted wirelessly (Bluetooth Low Energy, IR, RF, etc.). Furthermore, the processor may interpret/process the received data and send signals to actuators to control/drive/actuate the motors that drive the screwdrives, e.g. drive the pistons/plungers of the API. The data received by the handheld input device may represent the actual volume and rate of injection by the virtual handheld device. In another aspect, the data may simply be an "off/on" switch, which initiates ejection of the API when a signal is received and ejects it when the hand-held syringe stops moving or is pulled back from the barrel. will be stopped. In either case, data sent to the API by the input syringe or internal data collection related to ejection from the API barrel/plunger can be utilized to ensure the amount of fluid ejected from the API.

Further in the illustration of FIG. 2A, two finger rings or tabs 232 may receive the user's fingers during use. Note that throughout the description, cylindrical housing 202 and bore 204 are discussed. However, there are various configurations of the housing/bore 202/204 and piston/plunger 206/210 that may provide the functions and shapes (including rectangular, oval, triangular cross-sections, etc.) contemplated herein. However, it is not necessary to be restrictive in itself. Input syringe 200 also includes a Hall effect sensor module 250, which will be described in further detail below. One component of the Hall effect sensor module 250 may be a magnetic retaining ring 252 disposed on the exterior or outside surface of the syringe housing 202. In the illustrated embodiment, magnetic retaining ring 252 is positioned proximate proximal end 214b of housing 202, but may be positioned elsewhere along housing 202.

FIG. 2B shows a partial perspective cross-sectional view of input device 200 of FIG. 2A, showing Hall effect sensor module 250 (including, by way of example, 250a and 250b). Certain components 250a of the Hall effect sensor module 250 may be located within the interior chamber of the hollow shaft 208 of the plunger 206, and certain components 250b may be located on the exterior surface of the syringe housing. Various such components 250a, 250b are discussed in further detail below. The so-called internal component 250a (ie, the interior of plunger 206) may include a retaining insert 254a, 254b, a base or circuit board 256, and single or multiple Hall effect sensors 258 disposed thereon. Additionally, one or more batteries 260 and control switches 262 may be secured to circuit board 256. The signal from the Hall effect sensor 258 may first be processed by the circuit board 256 to determine the position of the plunger 206, the amount of medium in the syringe, etc., and then pass this information to the API receiver (or other related processing). system) via a transmitter 280. In another embodiment, for example, if a non-processing base 256 is used, the signal from each Hall effect sensor 258 is routed directly via transmitter 280 to an alternative associated system for processing the data/signal. May be sent.

Distal retention insert 254a may be inserted into shaft 208 proximate piston 210. Distal retention insert 254a may define a cavity 264. Air gap 264 may contain a wireless transmitter 280, such as a Bluetooth transmitter. Transmitter 280 may transmit signals from Hall effect sensor 258 to associated signal processing equipment as described herein. Alternative embodiments may utilize cable connections as described above. Proximal retention insert 254b is positioned within hollow shaft 208 near thumb ring 212. Both distal retention insert 254a and proximal retention insert 254b support, protect, and retain circuit board 256 within hollow shaft 208. Although two such components are configured for a tight fit within shaft 208, they may engage openings or slots in shaft 208 to prevent rotation of board 256 within shaft 208. A key or other protrusion may be provided. Although the retention inserts 254a, 254b may be permanently fixed within the shaft 208, configuring the inserts 254a, 254b to be removable may allow for replacement or repair of the circuit board 256, battery 260, etc. may be advantageous. In one embodiment, the thumb ring 212 may include a resilient base 264 that includes a plurality of protrusions 266 that may be engageable with a mating slot 268 of the shaft 208. Disengaging such protrusions 266 allows for removal of internal components, including retaining inserts 254a, 254b. A plurality of Hall effect sensors 258 are shown. Although more or fewer sensors 258 may be utilized in various embodiments, the use of a greater number of sensors 258 may increase the position of the plunger 206 (and thus the sensed input syringe). velocities and volumes). Hall effect sensor 258 is positioned linearly within the chamber substantially in line with or parallel to axis AS. Although the foregoing description includes the various components of the input syringe and their proximity to each other, such association is merely illustrative; the Hall effect sensor is attached to the housing and the magnetic component is secured to the plunger. It is clear that other configurations, including the structure described above, can be used to achieve the same results.

Further describing the shaft-mounted Hall effect sensor and housing-mounted magnet embodiments, the external component 250b, in the illustrated embodiment, includes a magnet retaining ring that may hold a plurality of magnets 270, such as arc magnets. 252 may be provided. Other embodiments may utilize cubic magnets, cylindrical magnets, or other magnets. The position of magnet 270 is fixed relative to and around the input syringe housing. Arc magnet 270 creates a substantially circular magnetic field through which shaft 208 (and Hall effect sensor 258) passes when shaft 208 is withdrawn from or inserted into the syringe bore. . The circular magnetic field allows the Hall effect sensor 258 to detect the magnetic field regardless of the rotational position of the plunger 206 about the axis AS. In other embodiments, magnet 270 may be secured directly to the syringe housing without a magnet retaining ring.

FIG. 2C shows a partially exploded perspective view of a portion of handheld input syringe 200 as seen in FIG. 2B. More specifically, plunger 206, Hall effect sensor module internal components 250a, and Hall effect sensor module external components 250b are illustrated.
Some of these components are generally illustrated in FIGS. 2A-2C and need not be further described. However, in the illustrated embodiment, both distal retention insert 254a and proximal retention insert 254b include molded recesses 272 that may be configured to receive and hold circuit board 256 in place. Recesses 272 may be placed within inserts 254a, 254b to conserve space within hollow shaft 208 of plunger 206. One or more batteries 260 may be located on the side of the circuit board 256 opposite the Hall effect sensors 258 (if the board requires some processing of the Hall effect sensor signals). Additionally, switch 262 may be located proximate battery 260 or elsewhere within hollow shaft 208. Switch 262 may, in certain embodiments, be a reed switch that detects movement of a plunger and moves to an engaged or actuated position. Switch 262 is not required, but may help conserve power when syringe 200 is not in use. Switch 262, when actuated, may selectively connect power from one or more batteries 260 to either or both of the plurality of Hall effect sensors 258 as well as wireless transmitter 280. In other embodiments, a manual switch such as a pull tab, button or rocker switch may be actuated by the user. In other examples, a single Hall effect sensor may be utilized instead of multiple sensors.

FIG. 3 shows a perspective view of another embodiment of a hand-held input syringe 300 that utilizes a Hall effect sensor module. Input syringe 300 may include a syringe housing 302 defining a hollow lumen. A plunger 306 including a shaft 308 and a piston 310 may be slidably received within the bore. Even if fluid is not being expelled from input syringe 300, piston 310 desirably maintains stability of shaft 308 as it advances within syringe housing 302. More specifically, the piston 310 may slidably engage the inner surface of the bore such that linear motion M of the shaft 308 within the bore causes the piston 310 to move. Movement M is carried out along the syringe axis As. Plunger 306 is moved back and forth within bore 304 by movement of a thumb pad, thumb ring 312, or alternative structure that provides plunger movement. As the plunger 306 moves in direction M towards the ejection end of the syringe housing 302 (opposite the thumb ring 312), the transmitter sends a wireless ( For example, Bluetooth, Wi-Fi, IR, RF, etc.) signals may be transmitted.

As an alternative to the embodiment shown in FIGS. 2A-2C, the Hall effect sensor module 318 may be secured to the outer surface of the syringe housing 302 rather than to the plunger. Hall effect sensor module 318 includes a Hall effect sensor housing 319 surrounding a plurality of Hall effect sensors 320. As discussed above with respect to FIGS. 2A-2C, increasing the number of individual Hall effect sensor elements may improve sensor accuracy. One or more leads or wires 324 may extend from the end of the Hall effect sensor module 318. Cable 316 may be connected to the API at end 328, as shown in FIG. In other embodiments, communications may be performed via wireless, Bluetooth, or other wireless connections, as described herein. The information may include the speed of movement of plunger 306 within housing 302, and thus may provide information regarding the total amount injected by the API in response to movement of plunger 306. As explained above, the signals from the Hall effect sensors may first be processed by the associated circuit board before being sent to the API, or the individual signals themselves may be sent to the API for processing.

In the embodiment shown in FIG. 3, the shaft 308 of the plunger 306 has one or more magnets 330 disposed on or within the shaft 308. In this case, magnet 330 may include multiple arc magnets disposed about shaft 308. As plunger 306 moves in direction M along axis As, magnet 330 passes in front of Hall effect sensor 320 of Hall effect sensor module 318. The magnetic field generated by magnet 330 is detected by Hall effect sensor 320. The Hall effect sensors 320 send signals to an interface unit that determines the position of the plunger 306 within the syringe housing 302 based on the position of the magnet 330 detected by the individual Hall effect sensors 320. Therefore, the position of plunger 306 can be determined. The interface may also determine various types of information listed above (as well as the speed of plunger movement). Two finger rings or tabs 332 may be present to receive the user's fingers during use. A stopper may be used to prevent plunger 306 from being withdrawn from syringe housing 302.

Although the embodiments shown in FIGS. 2A-3 depict multiple Hall effect sensors, other embodiments of handheld input devices may utilize one or more sensors of various types. For example, a single sensor or multiple sensors may be used to measure magnetic fields, material resistance, capacitance, optical transparency, etc. Measurements from such sensors may be utilized to determine the linear position and rate of movement of the plunger within the syringe. Examples of such sensors include, but are not limited to, Hall effect sensors (described in further detail herein), inductive sensors, capacitive touch sensors, and the like.

FIG. 4 shows a system 400 that utilizes a handheld input device/syringe 402 to drive/control an API 404. In this example, lead screw 406 may threadably engage movable screw drive element 408 . As shown, screw drive element 408 may be attached to plunger 410 of API syringe barrel 412 using plunger driver 414 . In this case, plunger 410, barrel 412 and plunger piston 416 may be offset from lead screw 406 and movable screw drive element 408, by way of example only. Additionally, as previously discussed, there may be numerous modes/motors that may be used to inject media with an automatic power injector, and this is only one example.

As further shown in FIG. 4, a motor 418 and a motor controller/actuator 420 may be present to rotate the lead screw 406, thereby converting linear motion of the movable drive element 408. The motor 418 and actuator/controller 420 may rotate in either direction, thereby driving the plunger 410 into the barrel 412 (to expel fluid from the barrel chamber 422) or retract it (to expel the medium from the barrel). into chamber 422).

In addition, as shown in FIG. 4, there may be a mechanism for measuring fluid discharged from the API 404. As shown, a fixed potentiometer 424 with a movable wiper blade 426 attached to the movable screw drive element 408 may assist in determining the amount of fluid expelled from the body chamber 422.

In another aspect, handheld input device 402 may be used to transmit signal S (wirelessly, as shown) to receiver 428 associated with API 404 . Signal receiver 428 may transmit signal information to processor 430 for processing the data. Processor 430 may then send a signal to motor controller/actuator 420 to drive motor 418 as communicated by handheld input device 402 . Ultimately, plunger 410 may be deployed to expel fluid from body chamber 422 into a conduit to the patient (eg, via a needle, catheter, etc. (not shown)).

FIG. 4 shows an arrangement in which a signal receiver 428 and a processor 430 may be housed within an API housing 432. However, signal receiver 428 and processor 430 may be separate entities, and the processed data/information is sent to a second transmitter/receiver (or more) between processor 430 and motor controller 420. It is contemplated that the signal may be transferred to the motor controller/actuator 420 by the motor controller/actuator 420 .

Additionally, FIG. 4 shows a measurement device (eg, potentiometer 424) that can be used to measure the amount of media (and, eg, injection rate) released by API 404. Additionally, handheld input device 402 may also be capable of providing emission measurement information/data, so this device may not be necessary.

In the example system 500 of FIG. 5, an API operator (such as a surgeon or other healthcare provider) may select various baseline parameters (such as flow rate, injection volume, rise time, maximum injection pressure, etc.) for the API 502. good. Such baseline parameters may be modified by flow diverting devices (electromechanical pressure compensation valves, electromechanical diverter tanks, etc.) or otherwise altered to further optimize the AC optimal injection profile (i.e. opacification). The injection profile may be modified to mimic (minimal contrast agent) to achieve For example, from FIG. 10, the baseline parameters may provide a profile that may look like a "typical API #1" injection. However, when using a flow diverter, as shown, the injection may be modified (eg, during processing or in real time) to produce a profile that is approximately the same as "API #1 with flow diverter".

FIG. 5 illustrates a system 500 that may utilize an input device 503 in the form of a hand-held input device to use the API 502 described above. As such, the illustrated system 500 may inherently capture information/data related to media emitted from or introduced into the chamber 504. In another aspect, the injector 502 may include a measurement device as shown in FIG. The system 500 of FIG. 5 includes a diverter circuit 515 that includes a diverter conduit 514 that is utilized in adjusting/changing fluid media to the patient P through the catheter 512 and through the diverter valve 510. FIG. 5 identifies two bypass routes 522, both of which include (to name a few considerations) the medium, the injection location at the patient site, and the conduit used to deliver the medium. and may be selected based on. Each path 522 may be provided with valves 518, 520 that allow for different flow rates. FIG. 5 also shows measurement devices such as a collection tank 530 and a pressure gauge 532. Media diverted from injection into patient P may be collected in tank 530. As shown, the pressure gauge 532 may be capable of determining the amount of fluid medium collected within the collection tank 530 as a result of the "head pressure" of the fluid within the collection tank 530. Pressure gauge 532 and collection tank 530 may be suspended from a bag holder (such as an IV bag pole) (not shown). In another aspect, collection tank 530 and measurement/sensing device (ie, pressure gauge 532) may be integrally configured as a single device. Additionally, information from pressure gauge 532, whether integrally or separately configured, may be sent to output display 534 by either a wired or wireless connection. In another example, the amount of media diverted may be displayed on a display located on API 502.

In determining the amount of media to be injected into patient P, the amount or volume of diverted media may be subtracted from the total amount or volume of media injected by injector 502. To accomplish this goal, a physician or system user simply reads two values from the output/data display 534 on the collection tank 530 and the display on the API (as shown in FIG. The amount may be determined. Conversely, there may be various ways of transmitting the information to be processed to a remote device (such as via a wired or wireless connection). The processor may be located in a separate component (eg, an iPad) or may be combined with the injector 502 and/or the measurement sensor device.

In one embodiment, data from the handheld input device and collection tank sensor (FIG. 5) may be delivered wirelessly (or via a wired connection) to a receiver and then to a processor (FIG. 4). ). Data from these two data measurements is used to calculate the volume of media injected into the patient (e.g., the total volume injected by API 502 minus the volume collected by collection tank 530). It's okay.

The diversion of media from the infusion through the diverter valve 510 has been shown to be an advantageous modulator/controller of the media actually delivered to the patient P by manual injection as well as injection by an automatic powered injector such as the API 502. ing. The diverter valve 510 may increase the resistance to flow of media into the diverter conduit 514 as the pressure of the injected media increases. That is, if there is little resistance to the injection from the injector (handheld or API 502), there will be a greater flow of media removed (through the flow diversion device) from the flow injected into the patient P. Conversely, if the pressure in the conduit 506/514/512 from the injector 502 to the patient P becomes too high, less will flow through the diversion conduit 514. In general, this type of adjustment ensures that the actual injection into patient P is appropriate for assessing a blood vessel or organ (for example) while buffering spikes in drug delivered to the patient (e.g., flattening the flow curve). It may be possible to quickly reach a flow rate to the patient that is beneficial to the patient. Additionally, flow diversion adjustments may maintain the "duration" of the injection, which may also be beneficial in visualization (ie, angiographic) evaluations. For example, in coronary angiography, if the injection into a coronary artery (at minimal flow rate) does not last more than about three heartbeats, the injection time may not be long enough to actually adequately visualize the artery. Thus, as an example, a person beating at 80 beats per minute (0.75 seconds/beat) may require at least 2.25 seconds (or more) to fully assess the coronary arteries. .

Figure 6 is from the SCAI 2020 Scientific Session, “Comparison of Contrast Injection Pressure Contours with Different Methods for Coronary Angio,” May 14-16, 2020. graphy (comparison of contrast agent injection pressure curves by various methods for coronary angiography)” We present some graphical results from the summary entitled. The summary disclosure is incorporated herein by reference in its entirety and can be found at http://scai. confex. com/scai/2020/meetingapp. It can be viewed at cgi/Paper/10225. As shown, in addition to a hand-held syringe, three automatic power injectors, API #1, API #2, and API #3, were used to inject the contrast agent. Performance testing included a digital pressure monitor attached to a three-way stopcock on the hub of a 4F angiography catheter. This manual injection was performed during coronary angiography by a cardiologist. All API settings were standardized at 3 ml/sec flow rate, 6 ml total volume, and 0.5 sec rise.

The collected data in Figure 6 is presented as pressure versus time. However, since P=Q*R, the actual pressure is directly related to the flow rate (Q). R is resistance, in this case the same catheter resistance R was tested in each situation. Since R was equivalent, both pressure vs. time curves would be directly related to the flow vs. time profile (of the same waveform). Furthermore, the total volume injected into the catheter of each profile (V=Q*T) directly indicates the area under each curve as shown. Note in Figure 6 that all automatic power injectors have some type of curve/flow profile. In fact, each API's curve results from the ability of each different API to rise rapidly, recede rapidly, and stop rapidly (e.g., the flow profile is not straight upward, but flat Q, straight descending). Additionally, there is compatibility with tube kits/manifolds etc. which may also affect performance. Due to the structure, it is necessary for the motor to increase the flow rate/pressure to a set value, release the pressure/flow rate at the set value, and immediately stop the injection. Therefore, there may be systemic structural challenges to the system to actually provide such an injection profile (such as FIG. 7) directly to the patient. As shown, the various APIs each have a unique injection profile based at least in part on the structure of its syringe, including, for example, the structure of its piston, plunger, and syringe barrel.

An exemplary injection profile (Q vs. T) is shown in FIG. In this case, injection into the left main coronary artery may be expected. As shown, a minimum flow rate Q is required to observe the contrast agent in the artery (Vi). This quantity Vi is shown in FIG. 7 as approximately 1.5 ml/sec, but may be between 1 ml/sec and 3 ml/sec, preferably between 0.5 ml/sec and 6.0 ml/sec. Furthermore, the flow rate required to inject into a patient may vary depending on the blood vessel or injection site. Referring to FIG. 7, the injection flow rate (Q) is insufficient to adequately opacify the vessel (regions A and B) or exceeds the amount necessary for opacification, thus leading to over-delivery of contrast agent. (Q) showing various regions (region C) that may have. That is, if the injection was controlled in the delivery of the contrast agent to obtain Vi (identified by the rectangle in the injection rate profile QAgent in Figure 7), to achieve the same result (e.g., It cannot be ruled out that the amount of contrast agent used may be reduced (by 25% to 30%) to sufficiently visualize the images. In another example, only 50% to 60% of the contrast agent to be delivered to the patient may be required to adequately visualize (ie, opacify) the blood vessels. Other examples are also contemplated, such as about 10% to about 70%, about 20% to about 60%, or other ranges. Depending on the injection and site, not only the minimum Q of opacification is important, but also the duration of the injection. If the period (number of seconds in Vi) is too short, the operator may not be able to understand what is being evaluated. If the duration (seconds in Vi) is too long, more contrast agent may be used than necessary.

As a practical matter, to further illustrate the complexity of efficiently delivering contrast media into the dynamic environment of the coronary arteries, some injector (e.g., syringe) operators must Some try to mimic rapid injection to minimize the area of A in FIG. 7 due to the rapid increase in flow rate). If sufficient opacification is "seen" on the radiograph, the operator may reduce the injection pressure (and volumetric flow rate). This approach may help reduce the area of A (reach Vi quickly). However, the operator may "overshoot" the delivery rate (ie, Vi) required for opacification, thus increasing the overinjection volume seen in region C of FIG. Note that it may be possible to inject at 100 psi or higher using a 10 cc (ml) syringe. This injection pressure from the syringe can produce a flow rate as high as 4.0 ml/sec, for example. This may exceed the flow rate that may be required to visualize blood vessels.

Referring back to FIG. 6, through the use of a flow diversion device to adjust/alter the injection into the patient, we have demonstrated that, on average, with a hand-held syringe, without compromising vessel visualization, A reduction in injection volume of up to 40% or more was experienced. However, in certain instances, the reduction per injection may vary from about 15% to about 60%, depending on, for example, the rate and pressure of injection. The results achieved may be as described in FIG. One of the advantages touted by automated power injector manufacturers is the ability to better control the delivery of contrast agent injected into a patient and thus reduce the amount of contrast agent injected. This may be partially true. However, as is clear from FIG. 6, it became clear that the three APIs tested did not have injection profiles close to the optimized curve shown in FIG. 7.

FIG. 7A shows an exemplary pulsatile media injection profile P _PulsatileI over a still typical 3.5 seconds of patient media injection. The intermediate injection profile P _PulsatileI of FIG. 7A may make it possible to achieve the full pressure of a typical injection, but the achievement is achieved at spaced intermediate pressures. In the example shown in FIG. 7A, the "duty cycle" (time between waves) of the pulsatile pressure profile P _PulsatileI may be approximately 0.25 seconds.

Referring to FIG. 8A, the injection profile of flow rate Q vs. time derived from API #1 with typical injector settings (Q=3, total injection volume=6 ml) is shown. The total amount used is the area under the curve. This is the infusion profile that is actually delivered directly to the patient.

Figure 8B shows that API #1 (Figure 8A) utilizes a flow diverter (described in Figure 5) to adjust the injection from the syringe with the same syringe settings as in Figure 8A (Q = 3, total volume = 6ml). FIG. 7 shows the infusion profile (Q vs. T) that would be delivered directly to the patient if modified.

FIG. 9A shows a typical injection profile output (Q vs. t) from API #1 shown in FIG. 8A, including an "opaque window" superimposed on the injection profile. Depending on the application, specific flow rates may be required or desirable to visualize blood vessels. Flow rates of about 0.5 to about 3.0 ml/sec, about 1.0 to about 2.0 ml/sec, and about 1.25 to about 1.75 ml/sec are contemplated, such as about 1.3, about 1 .5 and a flow rate of approximately 1.6 ml/sec. Visualizing the blood vessel to the patient may require a certain minimum flow rate as well as a duration of at least 2 seconds at or above the selected flow rate (Vi and duration described above with respect to FIG. 7). This window is shown shaded in Figure 9A, and as mentioned above, while flow rates below the threshold (Vi) can cause streaming (i.e., faint, insufficient opacification), this threshold Flow rates in excess of 10% can cause backflow of contrast from the target (in this example, the left main artery) to the aortic root.

Referring to FIG. 9B, the injection profiles of FIG. 8A (API #1) and FIG. 8B (API #1 with flow diverter) are superimposed on each other. Also highlighted in this example is the region (gray) where the API injection profile curve exceeds the diverted API #1 curve. Essentially, API #1 (alone) delivers excess contrast agent (i.e., perfusion) but maintains the flow rate, volume, and duration necessary (i.e., greater than Vi) to achieve sufficient image quality. do. This excess perfusion may not be necessary for radiographic imaging and may cause additional undesirable and unnecessary contrast agent load on the patient's kidneys. As shown, for example, a desired opacity window of 2 seconds duration is shown. Also of note in Figure 9B is that the combination (API #1 with flow diverter in Figure 5) was injected during the subsequent lower injection flow rate phase of approximately 2.5 seconds to 4.5 seconds of injection. There may be an additional benefit of reducing the amount of contrast agent used. This amount of contrast agent provides no additional imaging benefit.

There may be other advantages associated with the use of flow diversion devices in combination with automatic power injectors. Such benefits include, for example, lower peak pressures (or flow rates) and more constant (or flatter) profiles over time.

FIG. 10 illustrates changing the infusion input in the API and the resulting infusion profile for the patient. One curve is shown with a typical injection of API #1 (Q=3ml/sec, V=6ml). Next, what is superimposed is API #1 with a flow dividing device (almost the same as in FIG. 8B). In addition to these two curves, one profile shows the flow rate profile (Q vs. t) when keeping the flow rate the same (Q=3 ml/sec) and reducing the total volume of API #1 injection. As shown, the patient still has too much contrast injected and the duration of opacity of the vessels is insufficient. Additionally, lowering the flow rate further (Q = 2 ml/s) with a total volume of 4 ml may reduce some of the excess contrast injected into the patient, but does not provide enough medium for the injection time. there is a possibility. As previously discussed, visualization of the left main artery may require 2 to 4 heart beats or more.

In addition to the system described herein that utilizes the API in conjunction with a diversion tank, the proposed technique programs an algorithm that mimics the effect mechanically produced by the tank while eliminating the diversion tank from the system. We are considering replicating the injection profile by In such instances, we are considering including specific algorithms to control the operation of the API to mimic the effect of a diversion tank. Such a system may include the devices described herein and communication means and processors/controllers associated with the devices. The functionality of the algorithm may be programmed such that the API includes a profile more similar to the profile shown in FIG. 8B. As an example, such an algorithm may include generating increased pressure prior to opening the syringe barrel outlet. After opening the barrel outlet, the desired flow rate may be established quickly or instantaneously. Such flow rate may be maintained until a set flow duration is established. This algorithm also controls the operation of the motor in order to rapidly reduce the pressure (by reversing the flow rate), e.g. to reverse the operation of the motor (to generate a slight backflow). good. Consider other examples of algorithms that can mimic the functionality of systems that include diversion tanks. For example, algorithms and appropriate components may be used to actuate one or more valves that affect fluid flow from the API, e.g., to relieve pressure or divert flow. .

In additional examples, system 400 of FIG. 4 and system 500 of FIG. 5 may include a feedback loop to modify or otherwise augment the manually selected baseline parameters of the API (e.g., flow rate, injection volume, rise time, maximum injection pressure, etc.). In such examples, such selected baseline parameters may be modified, altered, or otherwise augmented by real-time feedback from various sensors (e.g., potentiometer 424, flow/pressure transducers associated with API body 504/422, pressure/flow sensors associated with injection into the patient, etc.) as well as any input devices (e.g., handheld device 402, etc.) to modify the injection profile to match a predefined optimal injection profile (i.e., minimum contrast to achieve opacification). For example, from FIG. 10, the baseline parameters may provide a profile that may appear to be a "typical API #1" injection. However, feedback from the sensors and input devices may modify the ongoing injection in real time to deliver an injection profile to the patient that is more similar to the profile achieved by "API #1 with diverter".

As mentioned above, the goal of obtaining optimal image opacity using the API is to pre-configure certain API variables (e.g., contrast agent injection flow rate, volume, rise time, and/or injection pressure). You can try to achieve this by setting Additionally, as previously discussed, the API operator may also seek to minimize the contrast agent load/dose to the patient. If the operator relies on pre-selected settings on the API, the user can adjust such settings prior to injection and/or use a variable speed manual controller to adjust the flow rate from the API in real time. In some cases, titration may be necessary. As a result, depending on the operator's interpretation of the fluoroscopic/x-ray image, the API settings may be further guided and/or the flow rate may be titrated using a manual controller or input device. In this case, the API operator is dependent on its real-time image/opacification assessment as well as the reaction time associated with the ability to achieve optimized opacification with minimal contrast agent volume.

Consider other examples that may allow for optimal image opacification while reducing the amount of contrast agent injected into the patient. For example, each API injection utilizes feedback from signals (data/information) obtained from fluoroscopic/X-ray images to drive the API drive mechanism (e.g., motor controller/actuator 420) may be directly (or indirectly) controlled, regulated, or otherwise provided. Other inputs are considered, such as EKG (pacing of heartbeats), pressure gauges associated with guide catheters, flow wires, etc., where the infusion may be adjusted to the filling of the coronary arteries, for example. Other inputs may also be used to provide feedback to control, change, or otherwise provide input to the injector. In this case, a perspective image will be described as an example, but other inputs may be used and the perspective image is just one example.

Furthermore, the opacity of the fluoroscopic/x-ray image may be evaluated via software to assist in determining in real time whether the opacity on the image needs to be increased or decreased. The processed data/information may be transferred to a motor controller/actuator 420, for example. Processed data may be implemented via one or more transmitters/receivers between processor 430 and motor controller 420. This data may be utilized to automatically adjust the API injection flow profile to reach and maintain the desired opacification over a set period of time. As mentioned above, the amount of time it takes for opacification to occur may be quantified in terms of the patient's heart rate per second. Additionally, API injection may be terminated after the desired opacity has been achieved and maintained for a desired "opacity window." Additionally, consider that operators/users may have individual preferences regarding opacity of regions. In this case, the operator/user (or another individual) may evaluate the "opacity" (eg, increase or decrease in opacity and/or increase or decrease the opacity duration). This evaluation may be performed post-injection or used to adjust future injections from the API. Additionally, this information allows the API (or other relevant data processing system) to determine the operator's preferences when performing future injections, as well as specific opacity requirements (site location, to name a few). patient size, heart rate, etc.). By way of example, prior to injection, the user can select the location to be treated (i.e., the left main coronary artery, below the knee vessel, a specific location within a blood vessel or organ, the entire left coronary artery branch, the right coronary artery, to name a few). arteries, PAD outflow, etc.). Additionally, data and/or Alternatively, the possibility of using evaluation cannot be denied.

APIs have a variety of uses and there are a variety of drugs that can be injected at multiple injection sites within a patient's body. Therefore, the examples above, including various flow rates, pressures, system operating times, etc., are for illustrative purposes only, and actual values may vary (significantly) between different injectors and applications. be. Examples of systems that operate with the algorithm are shown in FIGS. 12 and 13.

FIG. 11 illustrates an example of a suitable operating environment 1100 in which one or more of the present embodiments may be implemented. This is only one example of a suitable operating environment and is not intended to suggest any limitation as to scope of use or functionality. Other well-known computing systems, environments and/or configurations that may be suitable for use include personal computers, server computers, handheld or laptop devices, multiprocessor systems, microprocessor-based systems, smartphones, etc. programmable home appliances, network PCs, minicomputers, mainframe computers, smartphones, tablets, distributed computing environments including any of the systems or devices described above, and the like, but are not limited to those listed here.

Operating environment 1100, in its most basic configuration, typically includes at least one processing unit 1102 and memory 1104, which may be included, for example, in another device separate from the API, handheld syringe, or both. Depending on the exact configuration and type of computing device, memory 1104 (which stores, among other things, instructions for implementing the methods described herein) may include volatile memory (such as RAM), volatile memory (such as RAM, or flash memory). ) or some combination of the two. This most basic configuration is shown by line 1106 in FIG. Additionally, environment 1100 may include other storage devices (removable storage 1108 and/or non-removable storage 1110) including, but not limited to, magnetic or optical disks or tape. Similarly, environment 1100 may also include input devices 1114, such as a touch screen, keyboard, mouse, pen, voice input, etc., and/or output devices 1116, such as a display, speakers, printer, etc. Additionally, the environment may include one or more communication connections 1112 such as LAN, WAN, point-to-point, Bluetooth, RF, etc.

Operating environment 1100 typically includes at least some form of computer readable media. Computer readable media can be any available media that can be accessed by processing unit 1102 or other devices comprising an operating environment. By way of example, and not limitation, computer-readable media may include computer storage media and communication media. Computer storage media includes volatile and nonvolatile, removable and non-removable media implemented in any method or technology for storage of information such as computer-readable instructions, data structures, program modules or other data. included. Computer storage media may include RAM, ROM, EEPROM, flash memory or other memory technology, CD-ROM, digital versatile disk (DVD) or other optical storage device, magnetic cassette, magnetic tape, magnetic disk storage device or the like. magnetic storage, solid state storage, or any other tangible medium that can be used to store the desired information. Communication media embodies computer-readable instructions, data structures, program modules or other data in a modulated data signal, such as a carrier wave or other transmission mechanism, and includes any information delivery media. The term "modulated data signal" means a signal that has one or more of its characteristics set or changed in such a manner as to encode information in the signal. By way of example, and not limitation, communication media includes wired media, such as a wired network or direct wired connection, and wireless media, such as wireless media such as acoustic, RF, and infrared media. Combinations of any of the above should also be included within the scope of computer-readable media.

Operating environment 1100 may be a single computer operating in a network environment using logical connections to one or more remote computers. A remote computer may be a personal computer, server, router, network PC, peer device, or other general network node, and typically includes many or all of the elements listed above, as well as others not mentioned. Contains elements of. Logical connections include any methods supported by available communication media. Such networking environments are common in offices, enterprise-wide computer networks, intranets, and the Internet. In some embodiments, components described herein include modules or instructions executable by computer system 1100 that may be stored in computer storage media and other tangible media and transmitted over communication media. Computer storage media includes volatile and nonvolatile, removable and non-removable media implemented in any method or technology for storage of information such as computer readable instructions, data structures, program modules or other data. is included. In addition, any combination of the above must be included within the range of readable media. In some embodiments, computer system 1100 is part of a network that stores data on remote storage media used by computer system 1100.

FIG. 12 shows a method 1200 for controlling the evacuation of media from an autoinjector. Auto-injectors may be utilized in conjunction with input devices such as hand-held devices described elsewhere herein. The processor indicates the position of the input device plunger within the input device housing as well as other aspects of the input device trigger (e.g., the velocity at which the trigger/plunger deploys/retracts, the pressure applied to the trigger device, etc.) Signals from one or more sensors on the input device may be received. Such signals may be further processed by the processor and actuate the autoinjector accordingly. The processor may be located on the autoinjector, the input device, or may be multiple processors across multiple devices. In an example, since autoinjectors are typically not disposable, it may be advantageous to locate the processor on the autoinjector. Specific position sensors are described elsewhere herein. The method 1200 begins with an act 1202 of controlling an actuator to advance an ejector at a first speed based at least in part on an input device operation signal. Flow continues to operation 1204, where the actuator is controlled to advance the ejector at a second speed that is different than the first speed based at least in part on the injection signal received from the injection sensor. In examples, the infusion sensor (and associated signals) may be for pressure, volume flow, flow rate, etc. In the example, operation 1206 includes determining a target flow rate of the fluid medium near the infusion sensor. This target flow rate may be determined based on the injection signal. Thereafter, in operation 1208, the target flow rate may be maintained for a predetermined period of time. Here, the predetermined time may be measured from the time at which the target flow rate was determined or established. In other examples, the time may be based in part on time associated with a human heart rate. In still other examples, time may be a function of the input device, such as when an operator wishes to inject a short "puff" of contrast agent when positioning diagnostic and/or therapeutic equipment within the heart and/or its blood vessels. It may be a variable time. Furthermore, it is anticipated that there may also be a combination of preset time intervals and/or variable intervals. As an example, if the input device operates for less than a set time (eg, 1 or 2 seconds), short "puffs" may be allowed between injections. However, actuation of the input device beyond this time may trigger a preset injection interval. Further, if a signal is sent that the injection interval is longer than the preset amount, the injector may allow the API to continue injecting as a variable input signal. The examples given above are just a few examples where injections may be predetermined and/or variable.

FIG. 13 shows an example method 1300 for controlling the evacuation of media from an autoinjector. Method 1300 begins with act 1302 of receiving an input device operation signal from an input device located remotely (wired or wireless) from an autoinjector. Thereafter, an operation 1304 of processing the input device activation signal to obtain a first activation signal may be performed. A first actuation signal is transmitted at operation 1306. This signal activates the actuator to eject media from the autoinjector at a first rate. Thereafter, the user of the input device may change the forward speed or direction of the plunger (from forward to backward) for various reasons, such as specific procedure requirements, experience, etc. Such action causes a change signal to be received from at least one of an input device and a sensor (act 1308). This modification signal is then processed to obtain a second actuation signal (act 1310). This second actuation signal is then transmitted in operation 1312.

This disclosure has described several examples of the technology with reference to the accompanying drawings, which depict only some possible examples. However, other aspects may be embodied in many different forms and should not be construed as limited to the examples set forth herein. Rather, these examples are provided so that this disclosure will be thorough and complete, and will fully convey the scope of possible examples to those skilled in the art.

Although specific examples have been described in this specification, the scope of the present technology is not limited to such specific examples. Those skilled in the art will recognize other examples or improvements that are within the scope of the technology. Therefore, specific structures, acts, or media are disclosed by way of example only. Examples in accordance with the present technology may also combine elements or components that are generally disclosed but not explicitly illustrated in combination, unless otherwise noted herein. The scope of the technology is defined by the following claims and their equivalents.

Claims (20)

A system for injecting a medium into a patient, the system comprising:
An automatic injector,
a medium tank;
an ejector for ejecting a quantity of fluid medium from the medium tank;
an actuator coupled to the ejector;
an automatic injector comprising;
an input device remote from the actuator and communicatively coupled to the actuator;
a syringe housing;
a plunger slidably received within the syringe housing;
a circuit board coupled to a first component of the input device;
a plunger position sensor;
a battery coupled to the circuit board and configured to power the plunger position sensor;
a transmitter coupled to the circuit board for transmitting an input device operation signal to the autoinjector, the input device operation signal being based at least in part on a signal transmitted from a plunger position sensor; There is a transmitter and
an input device comprising;
a flow diversion device disposed downstream of the tank, the flow diversion device configured to receive at least a first portion of the quantity of fluid medium discharged from the media tank; ,
A system comprising: The system of claim 1, wherein the transmitter comprises a wireless transmitter and the automatic injector comprises a wireless receiver for receiving the input device operating signal. 2. The system of claim 1, wherein the input device further comprises a spring for biasing the plunger against the syringe housing. the medium tank comprises a syringe barrel;
the ejector includes a plunger slidably disposed within the syringe barrel;
2. The system of claim 1, wherein the actuator comprises a lead screw and a motor coupled to the lead screw, and rotation of the lead screw advances the ejector within the syringe barrel. The system of claim 4, wherein the automatic injector further comprises a position sensor for detecting a position of at least one of the ejector and the lead screw. The system of claim 1, further comprising a patient connection element downstream of the flow diverter for receiving at least a second portion of the quantity of fluid medium released from the medium tank. 7. The first portion of the amount of fluid medium and the second portion of the amount of fluid medium are comprised of the amount of fluid medium discharged from the media tank. system. 2. The system of claim 1, wherein the flow diversion device comprises a waste container for receiving at least a portion of the first portion of the quantity of fluid medium. The plunger position sensor comprises at least one Hall effect sensor coupled to the first component and a magnet coupled to a second component of the input device, the first component comprising: The system of claim 1, wherein the system is movable relative to the second component. 2. The system of claim 1, wherein the plunger position sensor comprises at least one of a light emitter, a light receiver, a potentiometer, and a magnet. A system for injecting a medium into a patient, the system comprising:
An automatic injector,
a medium tank;
an ejector for ejecting a quantity of fluid medium from the medium tank;
an actuator coupled to the ejector;
an automatic injector comprising;
an injection sensor located near the outlet of the media tank;
an input device remote from the actuator and communicatively coupled to the actuator;
a syringe housing;
a plunger slidably received within the syringe housing;
a circuit board coupled to a first component of the input device;
a plunger position sensor;
a battery coupled to the circuit board and configured to power the plunger position sensor;
a transmitter coupled to the circuit board for transmitting an input device operation signal to the autoinjector, the input device operation signal being based at least in part on a signal transmitted from a plunger position sensor; There is a transmitter and
an input device comprising;
a processor;
a memory for storing instructions, the instructions, when executed by the processor, causing the autoinjector to perform operations, the operations comprising:
controlling an actuator to advance an ejector at a first speed based at least in part on the input device operation signal;
controlling the actuator to advance the ejector at a second speed different from the first speed based at least in part on an injection pressure signal received from a pre-injection sensor; ,
A system equipped with The system of claim 11, wherein the processor and the memory are located on the automatic injector. 12. The system of claim 11, wherein the position sensor comprises at least one of a Hall effect sensor, a light emitter, a light receiver, a potentiometer, and a magnet. Controlling the actuator to advance the ejector at a second speed comprises:
determining a target flow rate of the fluid medium proximate the infusion sensor;
and maintaining the target flow rate for a predetermined time, the predetermined time being measured from a time at which the target flow rate was determined or a variable time as a function of an input device. 15. The system of claim 14, wherein the target flow rate is determined based at least in part on the injection pressure signal transmitted from the injection sensor. 15. The system of claim 14, wherein the target flow rate is determined based at least in part on a signal transmitted from a flow sensor. A method of controlling the injection of a medium into a patient using an automatic injector, the method comprising:
receiving an input device operation signal from an input device remote from the autoinjector;
processing the input device activation signal to obtain a first activation signal;
transmitting the first actuation signal, the first actuation signal actuating an actuator to eject the medium from the autoinjector at a first rate;
receiving a change signal from at least one of the input device and the sensor;
processing the modification signal to obtain a second actuation signal;
transmitting the second actuation signal based at least in part on the modification signal. 18. The method of claim 17, wherein the sensor is located remotely from the autoinjector. 19. The method of claim 18, wherein the sensor senses pressure within a media delivery system fluidly coupled to the autoinjector and the patient. 17. The method of claim 16, wherein the sensor is disposed within the autoinjector to sense the pressure of media within a media tank of the autoinjector.

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