Patent Publication Number: US-2023139275-A1

Title: Stopcock apparatus for angiography injector fluid paths

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application claims the benefit of U.S. Provisional Patent Application No. 62/990,145 filed on Mar. 16, 2020; U.S. Provisional Patent Application No. 62/990,170 filed on Mar. 16, 2020; and U.S. Provisional Patent Application No. 62/990,173 filed on Mar. 16, 2020, the disclosures of which are hereby incorporated by reference in their entireties. 
    
    
     BACKGROUND OF THE DISCLOSURE 
     Field of the Disclosure 
     The present disclosure relates generally to fluid path configurations and apparatuses for use with angiography fluid injectors for high pressure injection of medical fluids. More specifically, the present disclosure describes a fluid delivery system having a valve assembly configured to minimize potential administration of air to a patient during an injection procedure. 
     Description of Related Art 
     In many medical diagnostic and therapeutic procedures, a medical practitioner, such as a physician, injects a patient with one or more medical fluids. In recent years, a number of injector-actuated syringes and powered fluid injectors for pressurized injection of medical fluids, such as a contrast solution (often referred to simply as “contrast”), a flushing agent (such as saline or Ringer&#39;s lactate), and other medical fluids, have been developed for use in procedures such as cardiovascular angiography (CV), computed tomography (CT), ultrasound, magnetic resonance imaging (MRI), positron emission tomography (PET), and other imaging procedures. In general, these fluid injectors are designed to deliver a preset amount of fluid at a preset pressure and/or flow rate. 
     Typically, fluid injectors have at least one drive member, such as a piston, that connects to the syringe, for example via connection with a plunger or an engagement feature on a proximal end wall of the syringe. The syringe may include a rigid barrel with the syringe plunger being slidably disposed within the barrel. The drive members drive the plungers in a proximal and/or distal direction relative to a longitudinal axis of the barrel to draw fluid into or deliver the fluid from the syringe barrel. In certain applications, such as angiography, the medical fluids are injected directly into the cardiac system at fluid pressures up to 1200 psi. 
     During certain injection procedures at these high fluid pressures with fluid being administered directly to the cardiac system, it is imperative that no air or other gas bubbles be co-injected with the medical fluid as patient harm may result. Thus, new methods and devices are necessary to detect and prevent inadvertent injection of air during a high-pressure fluid injection procedure. To further complicate matters, at pressures of up to 1200 psi associated with some angiographic procedures, the flow rate of the medical fluid and the compressibility of air compresses any air in the system such that even if air is detected, initiating a shutdown of the injector may not occur fast enough to prevent the air from traversing a considerable distance downstream of the detection point. Furthermore, even if the injection is stopped upon air detection, the air volume may expand rapidly due to release of pressure caused by a system shutdown. In addition, release of system compliance upon cessation of an injection may result in continued fluid flow as the compliance volume is released in the absence of fluid pressure. 
     SUMMARY OF THE DISCLOSURE 
     In view of the foregoing, there exists a need for devices, systems, and methods for preventing air from being delivered to a patient during an injection procedure. Embodiments of the present disclosure are directed to a valve assembly for a fluid injector system, the valve assembly includes a valve housing, a first port configured for fluid communication with at least one syringe of a fluid injector, a second port, a third port, and a fourth port configured for fluid communication with a patient line. The valve assembly further includes an air detection region associated with the first port, a fluid path length fluid path length having a proximal end in fluid communication with the second port and a distal end in fluid communication with the third port, and a valve element defining a first valve fluid path and a second valve fluid path. The first valve fluid path provides fluid communication between the first port and the second port when in a delivery position of the valve housing relative to the valve element. The second valve fluid path provides fluid communication between the third port and the fourth port when in the delivery position. The third port is isolated from the fourth port when in a stop position of the valve housing relative to the valve element. 
     In some embodiments, thee valve assembly, further includes a fifth port configured for fluid communication with a bulk fluid source. The first fluid path provides fluid communication between the first port and the fifth port when in a fill position of the valve housing relative to the valve element. 
     In some embodiments, the fluid path length includes tubing having a length greater than a distance that an air bubble can travel or expand during an actuation time of the valve assembly. The actuation time of the valve assembly is a time interval between a time at which the air bubble is detected in the air detection region and a time at which the valve assembly reaches the stop position. 
     In some embodiments, the fluid path length includes tubing have a length of between approximately 1000 millimeters and approximately 1400 millimeters. 
     In some embodiments, the first port, the second port, the third port, and the fourth port are arranged circumferentially about the valve housing. 
     In some embodiments, the valve element is rotatable about a longitudinal axis of the valve housing between the delivery position and the stop position. 
     In some embodiments, the first port is offset relative to the second port along a longitudinal axis of the valve housing. 
     In some embodiments, the first port is integrally formed with the valve element and in fluid communication with the first valve fluid path. 
     In some embodiments, the valve housing is slidable relative to the valve element between the delivery position and the stop position. 
     In some embodiments, at least portions of the first valve fluid path and the second valve fluid path extend parallel to a longitudinal axis of the valve housing. 
     In some embodiments, fluid path length includes a plurality of longitudinal fluid channels arranged circumferentially about the valve housing, and a plurality of bent fluid channels connecting the plurality of longitudinal fluid channels in series. In some embodiments, the fluid path length includes coiled tubing. 
     Other embodiments of the present disclosure are directed to a fluid delivery system including at least one powered injector, at least one syringe, at least one air detector, a valve assembly, at least one controller in electrical communication with the at least one air detector. The at least one controller is configured for controlling fluid flow through the valve assembly. The fluid injector system further includes a patient line. The valve assembly includes a valve housing, a first port in fluid communication with the at least one powered injector, a second port, a third port, and a fourth port, a fluid path length having a proximal end in fluid communication with the second port and a distal end in fluid communication with the third port, and a valve element defining a first valve fluid path and a second valve fluid path. The patient line is in fluid communication with the fourth port. The first valve fluid path provides fluid communication between the first port and the second port in a delivery position of the valve housing relative to the valve element. The second valve fluid path provides fluid communication between the third port and the fourth port in the delivery position. The third port is isolated from the fourth port in a stop position of the valve housing relative to the valve element. 
     In some embodiments, the fluid delivery system further includes an actuator operably associated with the air detector and configured to transition the valve assembly to the stop position upon detection of air bubble by the air detector. The air detector is upstream of or within the first port and configured to detect an air bubble flowing out of the at least one syringe. 
     In some embodiments, the fluid path length includes tubing having a length greater than a distance that the air bubble can travel or expand during an actuation time of the valve assembly. The actuation time of the valve assembly is a time interval between a time at which the air bubble is detected by the air detector and a time at which the valve assembly reaches the stop position. 
     In some embodiments, the fluid delivery system further includes a bulk fluid source, the valve assembly further includes a fifth port in fluid communication with the bulk fluid source, and the first valve fluid path provides fluid communication between the first port and the fifth port when in a fill position of the valve housing relative to the valve element. 
     In some embodiments, the fluid path length includes tubing having a length greater than a distance that an air bubble can travel or expand during an actuation time of the valve assembly. The actuation time of the valve assembly is a time interval between a time at which the air bubble is detected in the air detection region and a time at which the valve assembly reaches the stop position. 
     In some embodiments, the fluid path length includes tubing have a length of between approximately 1000 millimeters and approximately 1400 millimeters. 
     In some embodiments, the first port, the second port, the third port, and the fourth port are arranged circumferentially about the valve housing 
     In some embodiments, the valve element is rotatable about a longitudinal axis of the valve housing between the delivery position and the stop position. 
     In some embodiments, the first port is offset relative to the second port along a longitudinal axis of the valve housing. 
     In some embodiments, the first port is integrally formed with the valve element and in fluid communication with the first valve fluid path. 
     In some embodiments, the valve housing is slidable relative to the valve element between the delivery position and the stop position. 
     In some embodiments, at least portions of the first valve fluid path and the second valve fluid path extend parallel to a longitudinal axis of the valve housing. 
     In some embodiments, the fluid path length includes a plurality of longitudinal fluid channels arranged circumferentially about the valve housing, and a plurality of bent fluid channels connecting the plurality of longitudinal fluid channels in series. 
     In some embodiments, the fluid path length includes coiled tubing. 
     Other embodiment of the present disclosure are directed to a method of trapping an air bubble in a fluid path length during an injection procedure performed by a fluid delivery system. The method includes detecting an air bubble flowing distally from at least one syringe and into a valve assembly with at least one air detector, the valve assembly including a including a first port, a second port, a third port, and a fourth port. The method further includes actuating the valve assembly to isolate the third port from the fourth port, thereby trapping the air bubble in the fluid path length between the second port and the third port. Actuating the valve assembly occurs within 60 and 100 milliseconds after detecting the air bubble with the air detector. 
     In some embodiments, the fluid path length includes tubing having a length greater than a distance that the air bubble can travel or expand during an actuation time of the valve assembly. The actuation time of the valve assembly is a time interval between a time at which the air bubble is detected and a time at which the third port is isolated from the fourth port. 
     In some embodiments, actuating the valve assembly includes rotating a valve element of the valve assembly relative to a valve housing of the valve assembly. 
     In some embodiments, actuating the valve assembly includes sliding the valve housing of the valve assembly relative to the valve element of the valve assembly. 
     In some embodiments, the fluid path length includes tubing have a length of between approximately 1000 millimeters and approximately 1400 millimeters. 
     In some embodiments, the valve assembly includes a valve housing. The first port, the second port, the third port, and the fourth port are arranged circumferentially about the valve housing. 
     In some embodiments, the valve assembly includes a valve element rotatable about a longitudinal axis of the valve housing between the delivery position and the stop position. 
     In some embodiments, the first port is offset relative to the second port along a longitudinal axis of the valve housing. 
     In some embodiments, the first port is integrally formed with the valve element. 
     In some embodiments, the valve housing is slidable relative to the valve element between the delivery position and the stop position. 
     In some embodiments, the valve element includes a first valve fluid path and a second valve fluid path. At least portions of the first fluid path and the second fluid path extend parallel to a longitudinal axis of the valve housing. 
     In some embodiments, the fluid path length includes a plurality of longitudinal fluid channels arranged circumferentially about the valve housing, and a plurality of bent fluid channels connecting the plurality of longitudinal fluid channels in series. In some embodiments, the fluid path length includes coiled tubing. 
     Further aspects or examples of the present disclosure are described in the following numbered clauses: 
     Clause 1. A valve assembly for a fluid injector system, the valve assembly comprising: a valve housing; a first port configured for fluid communication with at least one syringe of a fluid injector, a second port, a third port, and a fourth port configured for fluid communication with a patient line; an air detection region associated with the first port; a fluid path length having a proximal end in fluid communication with the second port and a distal end in fluid communication with the third port; and a valve element defining a first valve fluid path and a second valve fluid path, wherein the first valve fluid path provides fluid communication between the first port and the second port when in a delivery position of the valve housing relative to the valve element, wherein the second valve fluid path provides fluid communication between the third port and the fourth port when in the delivery position, and wherein the third port is isolated from the fourth port when in a stop position of the valve housing relative to the valve element. 
     Clause 2. The valve assembly of clause 1, further comprising a fifth port configured for fluid communication with a bulk fluid source, wherein the first fluid path provides fluid communication between the first port and the fifth port when in a fill position of the valve housing relative to the valve element. 
     Clause 3. The valve assembly of clause 1 or 2, wherein the fluid path length comprises tubing having a length greater than a distance that an air bubble can travel or expand during an actuation time of the valve assembly, wherein the actuation time of the valve assembly is a time interval between a time at which the air bubble is detected in the air detection region and a time at which the valve assembly reaches the stop position. 
     Clause 4. The valve assembly of any of clauses 1 to 3, wherein the fluid path length comprises tubing have a length of between approximately 1000 millimeters and approximately 1400 millimeters. 
     Clause 5. The valve assembly of any of clauses 1 to 4, wherein the first port, the second port, the third port, and the fourth port are arranged circumferentially about the valve housing. 
     Clause 6. The valve assembly of any of clauses 1 to 5, wherein the valve element is rotatable about a longitudinal axis of the valve housing between the delivery position and the stop position. 
     Clause 7. The valve assembly of any of clauses 1 to 6, wherein the first port is offset relative to the second port along a longitudinal axis of the valve housing. 
     Clause 8. The valve assembly of any of clauses 1 to 7, where the first port is integrally formed with the valve element and in fluid communication with the first valve fluid path. 
     Clause 9. The valve assembly of any of clauses 1 to 8, wherein the valve housing is slidable relative to the valve element between the delivery position and the stop position. 
     Clause 10. The valve assembly of any of clauses 1 to 9, wherein at least portions of the first valve fluid path and the second valve fluid path extend parallel to a longitudinal axis of the valve housing. 
     Clause 11. The valve assembly of any of clauses 1 to 10, wherein the fluid path length comprises: a plurality of longitudinal fluid channels arranged circumferentially about the valve housing; and a plurality of bent fluid channels connecting the plurality of longitudinal fluid channels in series. 
     Clause 12. The valve assembly of any of clauses 1 to 11, wherein the fluid path length comprises coiled tubing. 
     Clause 13. A fluid delivery system comprising: at least one powered injector; at least one syringe; at least one air detector; a valve assembly; at least one controller in electrical communication with the at least one air detector, wherein the at least one controller is configured for controlling fluid flow through the valve assembly; and a patient line, wherein the valve assembly comprises: a valve housing; a first port in fluid communication with the at least one powered injector, a second port, a third port, and a fourth port; a fluid path length having a proximal end in fluid communication with the second port and a distal end in fluid communication with the third port; and a valve element defining a first valve fluid path and a second valve fluid path; and wherein the patient line is in fluid communication with the fourth port, wherein the first valve fluid path provides fluid communication between the first port and the second port in a delivery position of the valve housing relative to the valve element, wherein the second valve fluid path provides fluid communication between the third port and the fourth port in the delivery position, and wherein the third port is isolated from the fourth port in a stop position of the valve housing relative to the valve element. 
     Clause 14. The fluid delivery system of clause 13, further comprising: an actuator operably associated with the air detector and configured to transition the valve assembly to the stop position upon detection of air bubble by the air detector, wherein the air detector is upstream of or within the first port and configured to detect an air bubble flowing out of the at least one syringe. 
     Clause 15. The fluid delivery system of clause 13 or 14, wherein the fluid path length comprises tubing having a length greater than a distance that the air bubble can travel or expand during an actuation time of the valve assembly, wherein the actuation time of the valve assembly is a time interval between a time at which the air bubble is detected by the air detector and a time at which the valve assembly reaches the stop position. 
     Clause 16. The fluid delivery system of any of clauses 13 to 15, further comprising a bulk fluid source, wherein the valve assembly further comprises a fifth port in fluid communication with the bulk fluid source, and wherein the first valve fluid path provides fluid communication between the first port and the fifth port when in a fill position of the valve housing relative to the valve element. 
     Clause 17. The fluid delivery system of any of clauses 13 to 16, wherein the fluid path length comprises tubing having a length greater than a distance that an air bubble can travel or expand during an actuation time of the valve assembly, wherein the actuation time of the valve assembly is a time interval between a time at which the air bubble is detected in the air detection region and a time at which the valve assembly reaches the stop position. 
     Clause 18. The fluid delivery system of any of clauses 13 to 17, wherein the fluid path length comprises tubing have a length of between approximately 1000 millimeters and approximately 1400 millimeters. 
     Clause 19. The fluid delivery system of any of clauses 13 to 18, the second port, the third port, and the fourth port are arranged circumferentially about the valve housing 
     Clause 20. The fluid delivery system of any of clauses 13 to 19, wherein the valve element is rotatable about a longitudinal axis of the valve housing between the delivery position and the stop position. 
     Clause 21. The fluid delivery system of any of clauses 13 to 20, wherein the first port is offset relative to the second port along a longitudinal axis of the valve housing. 
     Clause 22. The fluid delivery system of any of clauses 13 to 21, where the first port is integrally formed with the valve element and in fluid communication with the first valve fluid path. 
     Clause 23. The fluid delivery system of any of clauses 13 to 22, wherein the valve housing is slidable relative to the valve element between the delivery position and the stop position. 
     Clause 24. The fluid delivery system of any of clauses 13 to 23, wherein at least portions of the first valve fluid path and the second valve fluid path extend parallel to a longitudinal axis of the valve housing. 
     Clause 25. The fluid delivery system of any of clauses 13 to 24, wherein the fluid path length comprises: a plurality of longitudinal fluid channels arranged circumferentially about the valve housing; and a plurality of bent fluid channels connecting the plurality of longitudinal fluid channels in series. 
     Clause 26. The fluid delivery system of any of clauses 13 to 25, wherein the fluid path length comprises coiled tubing. 
     Clause 27. A method of trapping an air bubble in a fluid path length during an injection procedure performed by a fluid delivery system, the method comprising: detecting an air bubble flowing distally from at least one syringe and into a valve assembly with at least one air detector, the valve assembly comprising a comprising a first port, a second port, a third port, and a fourth port; and actuating the valve assembly to isolate the third port from the fourth port, thereby trapping the air bubble in the fluid path length between the second port and the third port, wherein actuating the valve assembly occurs within 60 and 100 milliseconds after detecting the air bubble with the air detector. 
     Clause 28. The method of clause 27, wherein the fluid path length comprises tubing having a length greater than a distance that the air bubble can travel or expand during an actuation time of the valve assembly, wherein the actuation time of the valve assembly is a time interval between a time at which the air bubble is detected and a time at which the third port is isolated from the fourth port. 
     Clause 29. The method of clause 27 or 28, wherein actuating the valve assembly comprises rotating a valve element of the valve assembly relative to a valve housing of the valve assembly. 
     Clause 30. The method of any of clauses 27 to 29, wherein actuating the valve assembly comprises sliding the valve housing of the valve assembly relative to the valve element of the valve assembly. 
     Clause 31. The method of any of clauses 27 to 30, wherein the fluid path length comprises tubing have a length of between approximately 1000 millimeters and approximately 1400 millimeters. 
     Clause 32. The method of any of clauses 27 to 31, and wherein the first port, the second port, the third port, and the fourth port are arranged circumferentially about the valve housing. 
     Clause 33. The method of any of clauses 27 to 32, wherein the valve assembly comprises a valve element rotatable about a longitudinal axis of the valve housing between the delivery position and the stop position. 
     Clause 34. The method of any of clauses 27 to 33, wherein the first port is offset relative to the second port along a longitudinal axis of the valve housing. 
     Clause 35. The method of any of clauses 27 to 34, where the first port is integrally formed with the valve element. 
     Clause 36. The method of any of clauses 27 to 35, wherein the valve housing is slidable relative to the valve element between the delivery position and the stop position. 
     Clause 37. The method of any of clauses 27 to 36, wherein the valve element comprises a first valve fluid path and a second valve fluid path, and wherein at least portions of the first fluid path and the second fluid path extend parallel to a longitudinal axis of the valve housing. 
     Clause 38. The method of any of clauses 27 to 37, wherein the fluid path length comprises: a plurality of longitudinal fluid channels arranged circumferentially about the valve housing; and a plurality of bent fluid channels connecting the plurality of longitudinal fluid channels in series. 
     Clause 39. The method of any of clauses 27 to 38, wherein the fluid path length comprises coiled tubing. 
     Further details and advantages of the various examples described in detail herein will become clear upon reviewing the following detailed description of the various examples in conjunction with the accompanying drawing figures. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG.  1    is a perspective view of a fluid delivery system according to an embodiment of the present disclosure; 
         FIG.  2    is a schematic view of a fluid delivery system in accordance with an embodiment of the present disclosure, with a valve assembly thereof in a delivery position; 
         FIG.  3    is a schematic view of the fluid delivery system of  FIG.  2   , with the valve assembly in a stop position; 
         FIG.  4    is a schematic view of the fluid delivery system in accordance with an embodiment of the present disclosure, with a valve assembly thereof in a fill position; 
         FIG.  5    is a schematic view of the fluid delivery system of  FIG.  4   , with the valve assembly in a delivery position; 
         FIG.  6    is a schematic view of the fluid delivery system of  FIG.  4   , with the valve assembly in a stop position; 
         FIG.  7    is a perspective view of a fluid delivery system including a valve assembly according to an embodiment of the present disclosure, with the valve assembly shown in a fill position; 
         FIG.  8    is a perspective view of a fluid delivery system of  FIG.  7   , with the valve assembly shown in a delivery position; 
         FIG.  9    is a side perspective view of the valve assembly of  FIG.  7   , with the valve assembly shown in the delivery position; 
         FIG.  10    is a bottom side perspective view of the valve assembly of  FIG.  9   ; 
         FIG.  11    is a top view of the valve assembly of  FIG.  9   ; 
         FIG.  12    is a side view of the valve assembly of  FIG.  9   ; 
         FIG.  13    is a bottom view of the valve assembly of  FIG.  9   ; 
         FIG.  14    is a cross-sectional top view of the valve assembly of  FIG.  12    along line A-A; 
         FIG.  15    is a cross-sectional side view of the valve assembly of  FIG.  12    along line X-X; 
         FIG.  16    is a cross-sectional bottom view of the valve assembly of  FIG.  12    along line B-B; 
         FIG.  17    is a cross-sectional side view of a fluid delivery system including a valve assembly according to an embodiment of the present disclosure, with the valve assembly in a fill position; 
         FIG.  18    is a cross-sectional side view of the fluid delivery system of  FIG.  17   , with the valve assembly in the fill position; 
         FIG.  19    is a cross-sectional top view of the fluid delivery system of  FIG.  17   , with the valve assembly in an intermediate stop position; 
         FIG.  20    is a cross-sectional side view of the fluid delivery system of  FIG.  17   , with the valve assembly in a delivery position; 
         FIG.  21    is a cross-sectional top view of the fluid delivery system of  FIG.  20   , with the valve assembly in the delivery position; 
         FIG.  22    is a cross-sectional side view of the fluid delivery system of  FIG.  17   , with the valve assembly in a full stop position; 
         FIG.  23    is a cross-sectional top view of the fluid delivery system of  FIG.  17   , with the valve assembly in the full stop position; 
         FIG.  24    is a side perspective view of a valve assembly according to an embodiment of the present disclosure; 
         FIG.  25    is a distal end view of the valve assembly of  FIG.  24   ; 
         FIG.  26    is a cross-sectional side view of the valve assembly of  FIG.  25    along line C-C; 
         FIG.  27    is a perspective view of a fluid delivery system including a valve assembly according to an embodiment of the present disclosure; 
         FIG.  28    is a cross-sectional side view of the fluid delivery system of  FIG.  27   ; and 
         FIG.  29    is a cross-sectional side view of a fluid delivery system including a valve assembly according to an embodiment of the present disclosure. 
     
    
    
     Referring to the drawings in which like reference characters refer to like parts throughout the several views thereof, the present disclosure is generally directed to an in-line air bubble suspension apparatus for use with an angiography injector system. 
     DETAILED DESCRIPTION 
     For purposes of the description hereinafter, the terms “upper”, “lower”, “right”, “left”, “vertical”, “horizontal”, “top”, “bottom”, “lateral”, “longitudinal”, and derivatives thereof shall relate to the disclosure as it is oriented in the drawing figures. Spatial or directional terms, such as “left”, “right”, “inner”, “outer”, “above”, “below”, and the like, are not to be considered as limiting as the invention can assume various alternative orientations. 
     As used herein, the singular form of “a”, “an”, and “the” include plural referents unless the context clearly dictates otherwise. 
     All numbers used in the specification and claims are to be understood as being modified in all instances by the term “about”. The terms “approximately”, “about”, and “substantially” mean a range of plus or minus ten percent of the stated value. 
     As used herein, the term “at least one of” is synonymous with “one or more of”. For example, the phrase “at least one of A, B, and C” means any one of A, B, and C, or any combination of any two or more of A, B, and C. For example, “at least one of A, B, and C” includes one or more of A alone; or one or more B alone; or one or more of C alone; or one or more of A and one or more of B; or one or more of A and one or more of C; or one or more of B and one or more of C; or one or more of all of A, B, and C. Similarly, as used herein, the term “at least two of” is synonymous with “two or more of”. For example, the phrase “at least two of D, E, and F” means any combination of any two or more of D, E, and F. For example, “at least two of D, E, and F” includes one or more of D and one or more of E; or one or more of D and one or more of F; or one or more of E and one or more of F; or one or more of all of D, E, and F. 
     It is also to be understood that the specific devices and processes illustrated in the attached drawings, and described in the following specification, are simply exemplary examples of the disclosure. Hence, specific dimensions and other physical characteristics related to the examples disclosed herein are not to be considered as limiting. 
     When used in relation to a component of a fluid delivery system such as a fluid reservoir, a syringe, or a fluid line, the term “distal” refers to a portion of said component nearest to a patient. When used in relation to a component of a fluid injector system such as a fluid reservoir, a syringe, or a fluid line, the term “proximal” refers to a portion of said component nearest to the injector of the fluid injector system (i.e. the portion of said component farthest from the patient). When used in relation to a component of a fluid delivery system such as a fluid reservoir, a syringe, or a fluid line, the term “upstream” refers to a direction away from the patient and towards the injector of the fluid injector system. For example, if a first component is referred to as being “upstream” of a second component, the first component is located nearer to the injector than the second component is to the injector. When used in relation to a component of a fluid delivery system such as a fluid reservoir, a syringe, or a fluid line, the term “downstream” refers to a direction towards the patient and away from the injector of the fluid delivery system. For example, if a first component is referred to as being “downstream” of a second component, the first component is located nearer to the patient than the second component is to the patient. 
     As used herein, the terms “capacitance” and “impedance” are used interchangeably to refer to a volumetric expansion of injector components, such as fluid reservoirs, syringes, fluid lines, and/or other components of a fluid delivery system as a result of pressurized fluids with such components and/or uptake of mechanical slack by force applied to components. Capacitance and impedance may be due to high injection pressures, which may be on the order of 1200 psi in some angiographic procedures, and may result in a volume of fluid held within a portion of a component in excess of the desired quantity selected for the injection procedure or the resting volume of the component. Additionally, capacitance of various components can, if not properly accounted for, adversely affect the accuracy of pressure sensors of the fluid injector system because the volumetric expansion of components can cause an artificial drop in measured pressure of those components. 
     The terms “first”, “second”, and the like are not intended to refer to any particular order or chronology, but refer to different conditions, properties, or elements. 
     All documents referred to herein are “incorporated by reference” in their entirety. 
     The term “at least” is synonymous with “greater than or equal to”. The term “not greater than” is synonymous with “less than or equal to”. 
     It is to be understood that the disclosure may assume alternative variations and step sequences, except where expressly specified to the contrary. It is also to be understood that the specific devices and processes illustrated in the attached drawings, and described in the following specification, are simply exemplary aspects of the disclosure. Hence, specific dimensions and other physical characteristics related to the examples disclosed herein are not to be considered as limiting. 
     Referring to the drawings in which like reference characters refer to like parts throughout the several views thereof, the present disclosure is generally directed to a fluid delivery system including at least one valve assembly for preventing delivery of air to a patient. Referring first to  FIG.  1   , an embodiment of a dual syringe angiography injector system (hereinafter “the fluid delivery system  1000 ”) is illustrated. The fluid delivery system  1000  is configured for injection of two medical fluids through first and second fluid paths  115 . A first of fluid paths  115  may be configured to inject a medical fluid, such as an imaging contrast media for an angiography injection procedure, and a second of fluid paths  115  may be configured to inject a flushing fluid, such as saline or Ringer&#39;s lactate. The fluid delivery system  1000  may include an injector housing  11  having two syringe ports  15  configured to engage two syringes  12 . In some embodiments, the syringes  12  may be retained within corresponding pressure jackets for example to prevent pressure-induced swelling and potential bursting of the syringes  12 . 
     The injector housing  11  may further include at least one graphical user interface (GUI)  16  through which an operator can view and control the status of an injection procedure. The GUI  16  may be in operative communication with a controller  400  (see  FIGS.  2 - 6   ) which sends and receives commands to and from the GUI  16 . 
     The fluid delivery system  1000  may further include at least one air detector  200  for detecting one or more air bubbles within an air detection region  120  of each fluid path  115 . The air detection region  120  may for example, be associated with a proximal portion of each fluid path  115 . In some embodiments, the at least one air detector  200  may be a single module having at least one sensor operatively associated with each of the fluid paths  115 . In some embodiments, the at least one air detector  200  may include at least two distinct modules, each module operatively associated with one of the fluid paths  115 . The at least one air detector  200  may be in operative communication with the controller  400  (see  FIGS.  2 - 6   ) such that the at least one air detector  200  may send and the controller  400  may receive signals from the at least one air detector  200  indicating the detection of the presence of one or more air bubbles in one or both of fluid paths  115  The at least one air detector  200  may include an ultrasonic sensor, optical sensor, or the like, configured to detect one or more air bubbles within the fluid paths. 
     Further details and examples of suitable nonlimiting powered injector systems, including syringes, controllers, air detectors, and fluid path sets are described in U.S. Pat. Nos. 5,383,858; 7,553,294; 7,666,169; 8,945,051; 10,022,493; and 10,507,319, the disclosures of which are hereby incorporated by reference in their entireties. While the fluid path elements described herein are illustrated in combination with a fluid injector system including syringes, other fluid delivery mechanisms, such as a pump, for example one or more peristaltic pumps, may be substituted for one or both of the syringes of the fluid delivery systems. 
     Referring now to  FIGS.  2 - 6    embodiments of the fluid delivery system  1000  further include at least one valve assembly  110 .  FIGS.  2 - 6    show a single syringe  12  of the fluid delivery system  1000 . For a fluid delivery system  1000  including multiple syringes  12 , such as the embodiment shown in  FIG.  1   , the components shown in  FIGS.  2 - 6    would be duplicated for each syringe  12  of the system (with the possible exception of the controller  400  and actuator  300 , which may control the components associated with all of the syringes  12 ). In addition, for a fluid delivery system  1000  including multiple syringes  12  and thus multiple valve assemblies  100 , the patient lines  55  extending from each valve assembly  110  may merge into a single fluid line (not shown) ultimately attached to the patient. In some embodiments, the fluid path assembly may include a fluid mixing connector element to merge fluid flow from each of the syringes  12  and ensure turbulent mixing of the two medical fluids. The fluid mixing connector element may include a mixing element to such as described in International Application No. PCT/US2021/019507, filed Feb. 25, 2021, and U.S. Pat. No. 9,555,379, the disclosures of which are hereby incorporated by reference in their entireties. 
     Referring first to  FIGS.  2  and  3   , the valve assembly  110  associated with the syringe  12  includes a plurality of ports, for example a first port  10 , a second port  20 , a third port  30 , and a fourth port  40 . Each of the ports is configured for connection and fluid communication with one or more other ports and one or more components of the fluid delivery system  1000  to facilitate fluid flow into, though, and/or out of the valve assembly  110 . The first port  10  may be configured for fluid communication with the syringe  12 , which injects medical fluid F under pressure into the first port  10  or takes in medical fluid F by applying a vacuum to the fluid through the first port  10 . The second port  20  may be configured for fluid communication with a proximal end of a fluid path length  135 , and the third port  30  may be configured for fluid communication with a distal end of the fluid path length  135 . The fourth port  40  may be configured for fluid communication with a patient line  55  which is in turn connected to a catheter or other device inserted into the vasculature of a patient. In some embodiments, the plurality of ports of the valve assembly  110  may further include a fifth port  50  configured for fluid communication with a bulk fluid container  21  used to fill the syringe  12  with medical fluid F (as shown in  FIGS.  4 - 6   ). 
     A controller  400  of the fluid delivery system  100  may be in operative communication with the syringe  12  and may be programmed or configured to actuate (e.g. reciprocally move) a plunger  13  to inject fluid from or take fluid into the syringe  12 . More generally, the controller  400  may include at least one processor programed or configured to execute one or more injection procedures according to one or more injection protocols stored in a memory of or accessible by the controller  400 . 
     With continued reference to  FIGS.  2  and  3   , the valve assembly  110  may include a valve housing  130  and a valve element  140  that are movable relative to one another to provide fluid communication various combination of the plurality of ports. In particular, the valve element  140  may define at least on fluid path providing fluid communication between a pair of the plurality of ports in a first position of the valve housing  130  relative to the valve element  140 , and fluid communication between a different pair of the plurality of ports in a second position of the valve housing  130  relative to the valve element  140 . Similarly, the at least one fluid path may provide fluid isolation between various ports in the first position and/or the second position of the valve housing  130  relative to the valve element  140 , such that fluid cannot flow between the isolated ports. In certain embodiments, the valve element  140  may provide a plurality, for example two, fluid paths providing selective fluid communication between the plurality of fluid ports depending on the relative position of the valve element  140  to the valve housing  130 . 
     Referring in particular to  FIG.  2   , the valve element  140  may define a first fluid path  150 , which, in a delivery position of the valve housing  130  relative to the valve element  140  as illustrated in  FIG.  2   , provides fluid communication between the first port  10  and the second port  20 , thereby allowing fluid communication between the syringe  12  and the proximal end of the fluid path length  135 . The valve element  140  may further define a second fluid path  160 , which, in the delivery position of the valve housing  130  relative to the valve element  140 , provides fluid communication between the third port  30  and the fourth port  40 , thereby allowing fluid communication between the distal end of the fluid path length  135  and the patient. Thus, in the delivery position, the first port  10  and second port  20  are in fluid communication via the first fluid path  150 , while the third port  30  and the fourth port  40  are in fluid communication via the second fluid path  160 . As such, fluid can flow from the syringe  12  into the first port  10 , from the first port  10  to the second port  20  via the first fluid path  150 , from the second port  20  to the third port  30  via the fluid path length  135 , from the third port  30  to the fourth port  40  via the second fluid path  160 , and from the fourth port  40  to the patient line  55 . The delivery position can thus be used to inject a patient with fluid F from syringe  12 . 
     The valve housing  130  and the valve element  140  may be moved relative to one another from the delivery position shown in  FIG.  2    to at least one stop position shown in  FIG.  3   . In the stop position, for example as illustrated in  FIG.  3   , the second fluid path  160  may isolate the third port  30  from the fourth port  40  thereby preventing fluid communication and fluid flow to the patient line  55 . In particular, the second fluid path  160  may interface with at least one inner wall  132  of the valve housing  130  to prevent fluid flow into and/or out of the second fluid path  160 . Similarly, in various embodiments, the first fluid path  150  may interface with an inner wall  132  of the valve housing  130  to prevent fluid flow into and/or out of the first fluid path  150 . It is noted that in  FIGS.  2 - 6   , the first fluid path  150  and the second fluid path  160  are shown in various orientations for ease of representation; and may not be reflective of the actual orientations of the first fluid path  150  and the second fluid path  160  in preferred embodiments of the present disclosure. 
     The valve assembly  110  may be moved to the stop position to prevent air from being injected into the patient. For example, the valve assembly  110  may be moved to the stop position when air is detected in the fluid delivery system  1000  upstream of the patient line  55 . In particular, an air detector  200 , such as an ultrasonic or optical sensor, may be operatively associated with an air detection region  120  along the fluid path  115  or within the first port  10 . The air detector  200  may be in operative communication with the controller  400  of the fluid delivery system  1000 . The air detector  200  and/or the controller  400  may be configured to detect the presence of one or more air bubbles in the fluid path  115  as the fluid F and air bubbles pass through the air detection region  120 . The controller  400  may also be in operative communication with the actuator  300  (e.g. a motor, linear actuator, solenoid, a rotating ball-screw motor, or other electromechanical motor) configured to move the valve assembly  110  between the delivery position, the stop position, and various other positions of the valve assembly  110  described herein. The controller  400  may be programmed or configured to activate the actuator  300  to move the valve assembly  110  to the stop position upon determining that at least one air bubble is present in the air detection region  120 . The controller  400  may also be in operative communication with an actuator of the fluid injector system  1000  (e.g. a motor, linear actuator, solenoid, a rotating ball-screw motor, or other electromechanical motor) configured to move the piston  13  and plunger  140  during a fluid injection procedure and may be programmed to stop movement of the piston  13  and plunger  140  during upon detection of at least one air bubble in the air detection region  120 . Thus, the fluid injector system  1000  may be configured to detect at least one air bubble in the air detection region  120  and in response the controller  400  may be configured to perform one or more operations that stops the fluid injection procedure (i.e., by halting movement of the piston  13  and plunger  14 ) and actuating the valve assembly  110  between the delivery position, the stop position, and various other positions of the valve assembly  110 . 
     Because response time of the actuator  300  and movement of the valve assembly  110  from the delivery position to the stop position is not instantaneous, the fluid path length  135  may be configured such that air detected in the air detection region  120  has insufficient time to reach the patient line  55  in the time required for the valve assembly  110  to reach the stop position. In particular, an actuation time of the valve assembly  110  may correspond to a time interval between a time at which the air bubble is detected in the air detection region  120  and a time at which the valve assembly  110  reaches the stop position. Depending on the design of the actuator  300 , the actuation time of the valve assembly  110  may be between approximately 60 milliseconds and approximately 100 milliseconds, for example in one embodiment approximately 80 milliseconds, between when one or more air bubble is sensed in the air detection region  120  by the at least one air detector  200  to when the valve actuator may actuate the valve assembly  110  from the delivery position to the stop position to stop a high pressure (e.g. 1200 psi) injection procedure via actuation of the valve assembly  110 . In some embodiments, the valve assembly  110  is moved to the stop position while the fluid pressure within the system is still high (e.g. 1200 psi) to prevent expansion of any air bubbles that would occur is a pressure drop was experienced. Even with this rapid response, at the high injection pressures and flow rates utilized during CV angiography injection procedures, the air bubble may still move from 2.8 mL to 3.6 mL of the volume of the fluid path over the 60 milliseconds to 100 milliseconds between detection of an air bubble and the valve assembly  110  reaching the stop position. For example, at approximately 1200 psi with conventional fluid path tubing diameters, an air bubble may travel a distance corresponding to 3.2 mL over 80 milliseconds at a flow rate of 30 mL/sec in a tubing with a 0.072 inch ID. The distance equivalence of 3.2 mL volume for such an embodiment may be approximately 4 feet of tubing length travelled during 80 milliseconds. In view of the distance travelled by the air bubble prior to the valve assembly reaching the stop position, the fluid path length  135  may have sufficient length and/or volume such that an air bubble cannot traverse or expand over the entire length of the fluid path length during the actuation time of the valve assembly  110 . As a result, actuation of the valve assembly  110  to the stop position, thereby isolating the patient line  55  from the fluid path length  135 , is effective to contain air bubbles within the fluid path length  135  before the air bubbles can be delivered to the patient. Further, if pressurization of the fluid is halted or reduced, the reduction in fluid pressure may result in volume expansion of the air bubble, further increasing the distance the air volume can travel/occupy in the fluid path after a detection event. Thus, the volume of the tubing associated the air detection region and valve assembly  110  must be sufficient to allow the system adequate time to shut the fluid flow to the patient, i.e., by stopping fluid communication between the fourth port  40  before the air bubble can pass through the fourth port  40 . The volume of the tubing may be a factor of one or more of inner tubing diameter, length of tubing, pliability or rigidity of the tubing, presence of one or more baffles and combinations thereof associated with the tubing. 
     In some embodiments, the fluid path length  135  is tubing having a length and associated fluid volume greater than a volume distance than an air bubble can travel or expand during the actuation time taken for the valve assembly  100  to transition from the delivery position to the stop position. For example, the tubing of the fluid path length  135  may be between approximately 1000 millimeters and approximately 1400 millimeters (or between approximately 3.5 feet and approximately 4.5 feet) long. In some embodiments, the tubing of the fluid path length  135  may be approximately 1200 millimeters (or approximately 4 feet) long. In some embodiments, the tubing of the fluid path length  135  may be coiled or wrapped to reduce the size of the fluid path length  135  and to prevent entanglement of the tubing with other components and individuals present in an injection room. The tubing of the fluid path length  135  may be coiled during an extrusion or post-extrusion process, for example where adjacent coils of the coiled length of tubing are adhered or otherwise connected together. In other embodiments, the coils of the coiled length of tubing may be loosely connected together, such as by a tie. In other embodiments, the length of tubing may be coiled or wrapped around a fixture to hold the fluid path length  135  in the coiled configuration. In some embodiments, the fluid path length  135  may include flow disrupting features and/or sections of increased diameter to slow the flow of air bubbles within the fluid path length  135 , as described for example in U.S. Provisional Patent Application No. 62/990,179, the disclosure of which is hereby incorporated by reference in its entirety. In other embodiments, the fluid path length  135  may be in a zig-zag configuration extending from the second port  20  to the third port  30  as described herein with reference to  FIGS.  27  and  28   . The approximately 1000 millimeters to approximately 1400 millimeters (or approximately 3.5 feet to approximately 4.5 feet) length of tubing  135  may be arranged in any manner between the second port  20  and the third port  30 , for example, may be stretched lengthwise, draped, wrapped, looped, or coiled to reduce the footprint of the tubing length. 
     Referring now to  FIG.  4   , in some embodiments the valve housing  130  and the valve element  140  may be moved relative to one another to a fill position in which fluid is drawn from the bulk fluid container  21  into the syringe  12 . In the fill position, the first fluid path  150  or the second fluid path  160  may provide fluid communication between the first port  10  and the fifth port  50  such that fluid may flow from the bulk fluid container  21  to the syringe  12 . In certain embodiments, the fill position may also be utilized to prime or purge one or more air bubbles from syringe  12  and the upstream fluid path  115  prior to a fluid injection procedure. The controller  400  may actuate (e.g. retract) the plunger  13  to draw fluid from the bulk fluid container  21  into the syringe  12 , for example through fifth port  50 , fluid path  160 , first port  10 , and fluid path  115 . The fill position of the valve assembly  110  may be used, for example, prior to an injection procedure to load and/or prime the syringe  12  with the desired type and volume of medical fluid for the injection procedure.  FIGS.  5  and  6    illustrate the fluid delivery system  1000  in the delivery position and stop position, respectively, for the embodiment of the valve assembly  110  having the fifth port  50  and bulk fluid source  21  for filling. Operation of the valve assembly  110  in the positions of  FIGS.  5  and  6    may be substantially similar as described with reference to  FIGS.  2  and  3   . 
     In the various embodiments of the valve assembly  110  described herein, the valve housing  130  and the valve element  140  may be movable relative to one another by any mechanical action, such as rotation or sliding. In some embodiments, the valve housing  130  may be configured to be substantially stationary and the valve element  140  may be configured to be moved relative to the valve housing  130 . In some embodiments, the valve element  140  may be configured to be substantially stationary and the valve housing  130  may be configured to be moved relative to the valve element  140 . In some embodiments, all of the plurality of ports  10 ,  20 ,  30 ,  40 ,  50  may be provided on the valve housing  130 . In other embodiments, all of the plurality of ports  10 ,  20 ,  30 ,  40 ,  50  may be provided on the valve element  140 . In other embodiments, some of the plurality of ports  10 ,  20 ,  30 ,  40 ,  50  may be provided on the valve housing  130 , and some of the plurality of ports  10 ,  20 ,  30 ,  40 ,  50  may be provided on the valve element  140 . The plurality of ports  10 ,  20 ,  30 ,  40 ,  50  may be arranged relative to one another in any manner that facilitates the desired fluid communication of the appropriate ports during the fill, delivery, and stop operations described herein. Similarly, the first fluid path  150  and the second fluid path  160  may be arrange in any manner that facilitates communication of the appropriate ports during the fill, delivery, and stop operations described herein. 
     Having generally and schematically described the components of the fluid delivery system  1000 , specific embodiments of the valve assembly  110  and its operation are described. 
     Referring now to  FIGS.  7 - 16   , in some embodiments, the valve assembly  110  may be in the form of a rotary, five-way high-pressure stopcock. It is to be understood that any features not particularly described with reference to  FIGS.  7 - 16    are understood to be identical or similar to the same features described with reference to  FIGS.  1 - 6   . As shown in  FIGS.  7 - 16   , the valve housing  130  of the five-way high-pressure stopcock  110  may be generally cylindrical in shape, and the plurality of ports (for example the first port  10 , the second port  20 , the third port  30 , the fourth port  40 , and the fifth port  50  as described herein) may be spaced circumferentially about the valve housing  130 . The valve element  140  may likewise be generally cylindrical in shape, form a fluid tight seal with the valve housing  130 , and may rotate about a longitudinal axis relative to the valve housing  130 . The plurality of ports may be offset from one another to provide clearance for the first fluid path  150  and the second fluid path  160  of the valve element  140 . For example, the first port  10  may be offset relative to the second port  20  along the longitudinal axis of the valve housing  130 . The valve element  140  may include an engagement feature  170 , such as a bore, boss, tab, gear, etc. for engaging the actuator  300  to facilitate movement of valve element  140  between various positions described herein. 
     With particular reference to  FIG.  7   , an embodiment of the fluid delivery system  1000  including the five-way high pressure stopcock  110  is illustrated in a fill position with fluid communication between the fifth port  50  and the first port  10 . The five-way high pressure stopcock  110  is attached via the fluid path  115  to a distal connector  105  of the syringe  12 . The air detection region  120  may be a portion of the fluid path  115  between the distal connector  105  and the first port  10  of the five-way high pressure stopcock  110  or may be located on the distal connector  105 . Alternatively, the air detection region  120  may be a portion of the first port  10 . The air detection region  120  is configured to be in operative communication with the air detector  200  (as shown in  FIGS.  2 - 6   ), such that air detector  200  can detect the presence of one or more air bubbles in fluid path  115  as the fluid passes through air detection region  120 . 
     With continued reference to  FIG.  7   , the fill position of the five-way high pressure stopcock  110  may provide fluid communication between the first port  10  and the fifth port  50 , such that the syringe  12  is fluid communication with the bulk fluid container  21 , to allow filling and/or priming of the syringe with a medical fluid during a filling operation. In the fill position, as the plunger  14  (see  FIGS.  1 - 6   ) associated with the syringe  12  is retracted, fluid flows in sequence from the bulk fluid container  21  through the fifth port  50 , the second fluid path  160 , the first port  10 , and the fluid path  115  into the syringe  12 . Also in the fill position, fluid communication between the syringe  12  and downstream components of the fluid delivery system  1000  is blocked to avoid inadvertent injection of fluid and potentially one or more air bubbles into the patient during a filling procedure. That is, the second fluid path  160  providing fluid communication between the first port  50  and the fifth port  50  is the only source of fluid communication with the syringe  12  when in the fill position. The first fluid path  150  of the valve element  140  is not in fluid communication with the syringe  12  or bulk fluid container  21 . 
     Once the filling operation and subsequent priming operation are completed, the five-way high pressure stopcock  110  may be transitioned to the delivery position shown in  FIG.  8    in preparation for an injection procedure. The controller  400  may move the five-way high pressure stopcock  110  to the delivery position by actuating the actuator  300  connected to the engagement feature  170  to rotate the valve element  140  relative to the valve housing  130 . In the delivery position, the five-way high pressure stopcock  110  may provide fluid communication between the first port  10  and the second port  20 , and fluid communication between the third port  30  and the fourth port  40 . As such, fluid injected from the syringe  12  may flow in sequence to the first port  10 , the second port  20  via the first fluid path  150 , the proximal end of the fluid path length  135  connected to the second port  20 , the third port  30  via the fluid path length  135 , the fourth port  40  via the second fluid path  160 , and finally to the patient line  55 . In the fluid delivery position, fluid may flow from the syringe  12  to the patient fluid line  55  over the course of an injection protocol until the total desired volume of medical fluid is delivered to the patient or until at least one air bubble is detected in the upstream air detection region  120 , as described herein. 
     According to some embodiments, the controller  400  is configured to rotate the valve element  140  of the five-way high pressure stopcock  110  to the stop position when air is detected in the fluid path  115  at the air detection region  120  by the air detector  200  (see  FIGS.  2 - 6   ), thereby and allowing for a rapid shutdown of fluid flow to the patient after detection of at least one air bubble by the air detector  200  even at the high pressures and fluid flow rates associated with angiography. In particular, the volume associated with the fluid path length  135  is sufficiently large enough that the air bubble cannot move from the air detector region  120  through to the fourth port  40  in the time that it takes the air detector  200  to communicate the air detection event to the controller  400  and for the controller  400  to actuate the five-way high pressure stopcock  110  and complete movement of the five-way high pressure stopcock  110  from the delivery position to the stop position, thereby preventing the air bubble from flowing to the patient. If at any time during the injection procedure the controller  400  detects air bubbles in the air detection region  120 , the controller  400  may rotate the valve element  140  via the actuator  300  to shut off fluid flow to system components downstream of the fluid path length  135 . For example, the valve element  140  may be rotated to a stop position (see e.g.  FIG.  6   ) in which the fourth port  40  is isolated from the third port  30 . As such, air bubbles detected in air detection region  120  do not have sufficient time to pass through the volume and length of the fluid path length  135  in the actuation time taken for the valve element  140  to reach the stop position. That is, once an air bubble is detected in fluid path  115 , the air detector  200  may transmit a signal to the controller  400  which then activates the actuator  300  to rotate the valve element  140  to the stop position, for example by rotating engagement feature  170 . Upon rotation of engagement feature  170 , the five-way high pressure stopcock  110  moves to the stop position, stopping fluid flow from the fluid path length  135  to the fourth port  40  and the patient line  55  connected thereto. 
     In various embodiments of the fluid delivery system  1000  during a high pressure (e.g., up to 1200 psi) injection procedure, after air is initially detected by the air detector  200 , it may take from 60 milliseconds to 90 milliseconds, for example in one embodiment approximately 80 milliseconds, for the controller  400  to stop an injection procedure. The total actuation time to stop an injection procedure may include time detecting an air bubble by the air detector  200 ; time communicating to the controller  400  that an air bubble has been detected; time for the controller  400  instructing the actuator  300  to rotate the five-way high pressure stopcock  110  to a stop position; and time until the patient line  55  is fully isolated from the fluid path length  135  to prevent continued fluid flow from one or more of rapid flow rate, compliance release (i.e., volume relaxation of pressure swollen syringe and fluid path components and release of up-taken mechanical slack in the fluid injector), and/or bubble expansion due to pressure lowering, so as to prevent the air bubble from continuing into the patient. At the high injection pressures typical of CV injection procedures, an air bubble may move from 2.8 mL to 3.6 mL of the volume of the fluid path over the 70 milliseconds to 100 milliseconds between detection of the air bubble and valve closing/injection halting. For example, at approximately 1200 psi, an air bubble may travel a distance corresponding to 3.2 mL over 80 milliseconds at a flow rate of 30 mL/sec in a tubing with a 0.072 inch ID. The distance equivalence of 3.2 mL volume for such an embodiment may be approximately 4 feet of tubing length travelled during 80 milliseconds. Thus, even with a rapid response time, an air bubble may travel a significant distance after air detection and before system shutdown. According to various embodiments of the fluid delivery system  1000  including the five-way high pressure stopcock  110  described herein, the fluid delivery system  1000  may at least temporarily contain the detected air bubble(s) in the fluid path length  135  and prevent the trapped air from being injected into the patient when actuated to the stop position. Upon an air detection event, the fluid injection procedure may be halted upon moving the five-way high pressure stopcock  110  to the stop position and typically the fluid injection and imaging procedure must be rescheduled or reinitiated from the start. It is understood that the volume and length of the fluid path length  135  may be appropriately selected based on injection protocol (i.e., maximum pressure and flow rate) and response time of one or more of the air detector  200 , controller  400 , actuator  300  of five-way high pressure stopcock  110 , and rotational distance necessary to move the valve element  140  to the full stop position. 
     According to various embodiments, the stop position may be any rotary position of the valve element  140  where the fourth port  40  and the patient line  55  are fluidly isolated from (i.e. not in fluid communication with) either the first fluid path  150  or the second fluid path  160  or both. Because of the relative positions of the first fluid path  150  and the second fluid path  160  of the valve element  140  relative to the fourth port  40 , only minor rotational actuation of engagement feature  170  may be required to move the five-way high pressure stopcock  110  from the delivery position to the stop position. For example, the valve element  140  may only need to be rotated so that the second fluid path  160 , which is in fluid communication with the fourth port  40  in the delivery position, interfaces with an inner wall  132  of the valve housing  130  not occupied by the fourth port  40 . 
     According to various embodiments, the five-way high pressure stopcock  110  may include an intermediate stop position. In the intermediate stop position, fluid flow within the system is stopped, having a similar or identical effect to the full stop position shown in  FIG.  6   . To reach the intermediate stop position, the valve element  140  of the five-way high pressure stopcock  110  may be rotated by the actuator  300  to a position relative to the valve housing  130  such that fluid communication between the bulk fluid container  21  and the syringe  12  is blocked. Further, in the intermediate stop position, fluid communication between the syringe  12  and the patient fluid line  55  via fourth port  40  is blocked, for example by blocking fluid communication between the fluid path length  135  at the third port  30  and the patient line  55  connected to the fourth port  40  and/or by blocking fluid communication between the fluid path length  135  at the second port  20  and the syringe  12  connected to the first port  10 . The intermediate stop position may allow for all fluid communication within the five-way high pressure stopcock  110  to be ceased without having to transition through another position, such as the fill position or the delivery position. In certain embodiments, the intermediate stop position may be used to prevent pressurized backflow of fluid from a second syringe of the fluid delivery system  1000  (not shown) into the five-way high pressure stopcock  110  and the first syringe  12  or other upstream component of the first syringe fluid path system. For example, if a second syringe is pressurized and in fluid communication, for example, via a downstream fluid mixing connector, with an unpressurized first syringe or a first syringe having a lower fluid pressure, the pressurized fluid from the second syringe may flow upstream into the fluid path components and even the first syringe. In some embodiments, the intermediate stop position may allow pre-pressurization of medical fluid in the syringe  12  prior to moving the five-way high pressure stopcock  110  to the delivery position so that the entire fluid path system is not under the high pressure of the pre-pressurized syringe. This may have the advantage of taking up capacitance in the syringe and components (i.e., accounting for increase fluid volume due to swelling of the syringe and components under high pressure) and/or taking up mechanical slack in the fluid delivery system  1000  to provide a more accurate fluid delivery volume. In other embodiments, pre-pressurization of a medical fluid in syringe  12  may provide smoother pressure/flow transitions when switching between injection of a more viscous medical fluid and a less viscous medical fluid, such as contrast and saline, respectively. Examples of injection protocols using pre-pressurization to prevent fluid flow spikes during fluid transitions are described in International PCT Publication Nos. WO 2019/046260 and WO 2019/046259, the disclosures of which are hereby incorporated by reference in their entireties. In other embodiments, the intermediate stop position may allow for detection of air within the fluid delivery system  1000  by pressurization of the syringe  12  contents prior to the injection procedure, as described in International PCT Publication No. WO 2019/204605, the disclosure of which is hereby incorporated by reference in its entirety. In other embodiments, the intermediate stop position may allow for vacuum coalescence and purging of air bubbles from the syringe system prior to the injection protocol, as described in International PCT Publication No. WO 2019/204617, the disclosure of which is hereby incorporated by reference in its entirety. 
     While  FIGS.  7  and  8    show the fluid path length  135  as a coiled length of tubing, the fluid path length  135  may be any of the various embodiments discussed herein with reference to  FIGS.  2 - 6   . For example, the fluid path length  135  may include a length of tubing such as between approximately 1000 and approximately 1400 millimeters, or a length of tubing or approximately 1200 millimeters (or between approximately 3.5 feet and approximately 4.5 feet, or a length of tubing of approximately 4 feet). In some embodiments, such as shown in  FIGS.  7  and  8   , the tubing of the fluid path length  135  may be coiled to reduce the “foot-print” of the fluid path length  135  and allow the fluid delivery system  1000  including the five-way high pressure stopcock  110  to occupy a small amount of space next to the injector housing  11 . 
     Referring now to  FIGS.  9  to  16   , various views of the five-way high pressure stopcock  110  are provided according to specific embodiments of the present disclosure to more readily illustrate the various fluid flow paths described herein and the interconnectedness of the various ports in different configurations and positions. As described with reference to  FIGS.  7  and  8   , the valve housing  130  may be rotatably and sealably engaged with the valve element  140 , such that fluid even under the high pressure a CV injections cannot flow between the valve housing  130  and the valve element  140  except through the ports  10 ,  20 ,  30 ,  40 ,  50  and the fluid paths  150 ,  160 . As shown in  FIGS.  9 - 16   , the plurality of ports of the five-way high pressure stopcock  110  may be arranged around the periphery of the valve housing  130  in an arrangement that facilitates selective fluid communication between the ports depending on whether the fill position, the delivery position, the stop position, or the intermediate stop position is required. According to an embodiment, the first port  10 , the third port  30 , the fourth port  40 , and the fifth port  50  may be located in a same longitudinal plane around the periphery of the valve housing  130 , whereas the second port  20  may be offset towards the top of the valve housing  130  relative to the other ports. The first fluid path  150  may be slanted diagonally relative to the longitudinal axis of the valve housing  130  and/or relative to the planes occupied by the ports  10 ,  20 ,  30 ,  40 ,  50  in order to provide necessary clearance for the first fluid path  150  and the second fluid path  160  to establish fluid communication with the appropriate ports in the fill position, stop position, and delivery position described herein. The second fluid path  160  may be perpendicular to the longitudinal axis of the valve housing  130 , or parallel to the planes occupied by the ports  10 ,  30 ,  40 ,  50 . 
     According to the embodiment shown in  FIGS.  9  to  16   , in the delivery position, fluid communication is provided between the first port  10  and the offset second port  20  by the diagonal first fluid path  150 . As such, fluid communication is provided between the syringe attached to the first port  10  and the fluid path length  135  connected to the second port  20  (see  FIG.  8   ). Also in the delivery position, fluid communication is provided by the second fluid path  160  in the plane between the third port  30  and the fourth port  40 . As such, fluid communication is provided between the fluid path length  135  connected to the third port  30  and the patient line  55  connected to the fourth port  40  (see  FIG.  8   ). Also in the delivery position, fluid communication between the fifth port  50  and the first port  10  in blocked, such that the syringe  12  is not in fluid communication with the bulk fluid container  21 . 
     In contrast, in the fill position (see  FIG.  7   ), fluid communication between the first port  10  and the fifth port  50  is provided by the second fluid path  160  in the plane between the first port  10  and the fifth port  50 . Also in the fill position, fluid communication is blocked between the third port  30  and the fourth port  40  by the diagonal nature of the first fluid path  150  which does not interconnect the co-planar third port  30  and fourth port  40 . Instead, the distal end of the first fluid path  150  abuts an inner wall  132  of valve housing  130  (see  FIG.  4   ). 
     Referring specifically to  FIGS.  14  to  16   , a series of cross-sectional views along the various section lines of  FIG.  12    are illustrated in the delivery position.  FIG.  14    illustrates a cross-sectional top view of the five-way high pressure stopcock  110  along line A-A of  FIG.  12   . As shown in  FIG.  14   , the first fluid path  150  provides fluid communication between the first port  10  and the second port  20 . The second fluid path  160  (shown in dashed lines as the second fluid path  160  does not intersect plane A-A) provides fluid communication between the third port  30  and the fourth port  40 .  FIG.  15    illustrates a cross-sectional side view of the five-way high pressure stopcock  110  along line X-X of  FIG.  12   . As shown in  FIG.  15   , fluid communication to the fifth port  50  is blocked in the delivery position.  FIG.  16    illustrates a cross-sectional bottom view of the five-way high pressure stopcock  110  along line B-B of  FIG.  12   . As shown in  FIG.  16   , the first fluid path  150  provides fluid communication between the first port  10  and the second port  20  (note that the first fluid path  150  is shown in dashed lines near the second port  20  where its diagonal nature leaves plane B-B). The second fluid path  160  provides fluid communication between the third port  30  and the fourth port  40 . 
     Referring now to  FIGS.  17 - 28   , in some embodiments of the present disclosure, the valve assembly  110  may be in the form of a high-pressure linear stopcock. It is to be understood that any features not particularly described with reference to  FIGS.  17 - 28    are understood to be identical or similar to the same features described with reference to  FIGS.  1 - 16   . Referring first  FIG.  17   , the valve housing  130  of the high-pressure linear stopcock  110  may be generally cylindrical in shape, and the plurality of ports (for example the second port  20 , the third port  30 , the fourth port  40 , and the fifth port  50 ) may be arranged along a length of the valve housing  130 . In some embodiments, the second port  20 , the third port  30 , and the fifth port  50  may extend radially from a sidewall of the valve housing  130 , and the fourth port  40  may extend from a distal end of the valve housing  130 . 
     The valve element  140  may likewise be generally cylindrical in shape and may be slidable relative to the valve housing  130  along a longitudinal axis relative to the valve housing  130 . The valve element  140  may form a fluid tight seal relative to the valve housing  130  via one or more O-rings  116  or elastomeric seals arranged between the valve element  140  and the valve housing  130 , for example along the valve element  140  and between the various ports. Further, the one or more O-rings  116  allow the linear stopcock  110  to more readily withstand the high fluid pressures associated with an angiographic injection procedure because the pressures are balanced on each side of the one or more O-rings  116 . 
     The first port  10  configured for connection to the syringe  12  may be provided on (e.g. integrally formed with) a proximal end of the valve element  140 , such that the first port  10  moves relative to the other ports (i.e. the second port  20 , the third port  30 , the fourth port  40 , and the fifth port  50 ) when the valve housing  130  is moved relative to the valve element  140 . Further, the first port  10  may be in constant fluid communication with the first fluid path  150  due to the first port being a part of the valve element  140 . The air detection region  120  may also be provided directly on, or comprise a portion of, the proximal end of the valve element  140 . 
     Because the syringe  12  of the fluid delivery system  1000  is typically stationary, in some embodiments the valve element  140  connectable to the syringe  12  is also stationary. As such, the actuator  300  moves the valve housing  130  relative to the valve element  140  in order to actuate the high-pressure linear stopcock  110  between the various positions described herein. In other embodiments, the valve element  140  may slide whereas the valve housing  130  remains substantially stationary. As the valve housing  130  slides relative to the valve element  140  (or vice versa), the high-pressure linear stopcock  110  moves between the fill position, the intermediate stop position, the delivery position, and the full stop position as described herein. One or more biasing members and/or motor may be used to actuate high-pressure linear stopcock  110  as described herein. 
     With continued reference to  FIGS.  17 - 23   , the first fluid path  150  and the second fluid path  160  are defined in the valve element  140 . At least portions of the first fluid path  150  and the second fluid path  160  path may extend parallel to and/or coaxial with a longitudinal axis of the valve element  140 . Further, portions of the first fluid path  150  and the second fluid path  160  extend out of the valve element  140  into the valve housing  130  for communication with the various ports depending on the position of the valve housing  130  and ports relative to the valve element  140  and the corresponding fluid paths  150 ,  160 . As with the embodiments of  FIGS.  2 - 16   , the first port  10  of the high-pressure linear stopcock  110  may be configured for connection to a distal connector  105  of the syringe  12 , the second port  20  may be configured for connection to a proximal end of the fluid path length  135 , the third port  30  may be configured for connection to the distal end of the fluid path length  135 , the fourth port  40  may be configured for connection to the patient line  55 , and the fifth port  50  may be configured for connection to bulk fluid container  21  (via bulk fluid container line  22  shown in  FIGS.  17 - 20   ). 
       FIGS.  18 ,  21 , and  23    show an additional air detector  201  and associated air detection region  121 . In particular, the air detection region  121  may be a portion of the fluid path length  135  in proximity to the second port  20 , such that the air detector  201  may be configured to detect air bubbles flowing into the proximal end of the fluid path length  135 . Communication between the air detector  201  and the controller  400  may be substantially the same as communication between the air detector  200  and the controller  400 . In some embodiments, the air detector  201  and the air detection region  121  may be provided in addition to the air detector  200  and the air detection region  120 . In some embodiments, the air detector  201  and the air detection region  121  may be provided in place of the air detector  200  and the air detection region  120 . 
     With continued reference to  FIGS.  17 - 20   , the actuator  300  of the high-pressure linear stopcock  110  includes a biasing member  310 , such as a valve spring, which biases the valve housing  130  to the full stop position. The controller  400  (see  FIGS.  2 - 6   ) may activate the actuator  300  to overcome the bias of the biasing member  310  to hold the valve housing  130  in any of the fill position, the delivery position, or the intermediate stop position. If air is detected by the air detector  200  (see  FIGS.  2 - 6   ), the controller  400  may be configured to deactivate the actuator  300  such that the biasing member  310  automatically returns the valve housing  130  to the full stop position. The actuator  300  may be an electromechanical motor, such as a solenoid, a rotating ball-screw motor, or other electromechanical motor. The actuator  300  may further include an electromechanical clutch  330  that engages a motor drive assembly  315  with the slidable valve housing  130  and allows the motor to slidably control the valve housing  130  and move the high-pressure linear stopcock  110  between the fill, delivery, full stop, and intermediate stop positions. The electromechanical clutch  330  is in operable communication with the controller  400  and is configured to disengage the motor drive assembly  315  from the slidable valve housing  130  when air is detected in the air detection region  120  by the air detector  200 . Disengaging the electromechanical clutch  330  from the motor drive assembly  315  releases the biasing member  310  which then rapidly moves the high-pressure linear stopcock  110  to the full stop position, shutting off fluid flow from the fluid path length  135  to the patient line  55  and preventing the flow of the detected air bubble through the fourth fluid port  40  and into the patient&#39;s vasculature system. Alternatively, in certain embodiments, the motor drive assembly  315  may actuate the motor drive assembly  315  to move to the full stop position upon detection of one or more air bubbles in air detection region  120 . 
     In some embodiments, the biased clutch mechanism allows for a rapid shutdown of fluid flow to the patient after detection of at least one air bubble by the air detector  200 . For example, in various embodiments of the system  1000  during a high pressure (e.g., 1200 psi) injection procedure, when air is detected by the air detector  200 , the valve housing  130  may take from 60 milliseconds to 90 milliseconds, for example approximately 80 milliseconds, to slide the from the delivery position to the full stop position once the actuator  300  is deactivated. Upon activation of the electromechanical clutch  330 , the biased valve housing  130  quickly moves to the full stop position, stopping fluid flow from the fluid path length  135  to the patient line  55 . The total actuation time to stop an injection procedure may include time detecting an air bubble by the air detector  200 ; time communicating to the controller  400  that an air bubble has been detected; time for the controller  400  instructing the actuator  300  to release the valve housing  130 , the time it takes for the biasing member to move the biased valve housing  130  to the full stop position relative to the valve element  140 ; and the time until the patient line  55  is fully isolated from fluid path length  135  to prevent fluid continued fluid flow from one or more of rapid flow rate, compliance release and/or bubble expansion from continuing into the patient. 
     Referring particularly to  FIGS.  17  and  18   , the fill position of the high-pressure linear stopcock  110  is illustrated according to an embodiment of the present disclosure. In the fill position, the valve housing  130  may be in a maximum distal position relative to the valve element  140 . In one embodiment, the valve housing  130  is slid relative to the valve element  140  such that the first port  10  is in fluid communication with the fifth port  50  via the first fluid path  150 . As such, the syringe  12  is in fluid communication with the bulk fluid container line  22  such that the syringe  12  can draw fluid from the bulk fluid container  21  (see  FIGS.  2 - 6   ). The second port  20  may be isolated such that no flow into or out of the proximal end of the fluid path length  135  is possible. Also in the fill position, the third port  30  may be in fluid communication with the fourth port  40  due to valve housing  130  being in a distalmost position relative to the valve element  140 . However, as the fluid path length  135  is isolated at the second port  20 , there is no flow between the third port  30  and the fourth port  40 . In other embodiments, the various ports may be configured so that the third port  30  is not in fluid communication with the fourth port  40 , when in the fill position. 
     Referring now to  FIG.  19   , an intermediate stop position of the high-pressure linear stopcock  110  is illustrated according to an embodiment of the present disclosure. In the intermediate stop position, the valve housing  130  is moved proximally relative to the fill position. In the intermediate stop position, fluid flow within the system is stopped. The valve housing  130  is moved by the actuator  300  to a position relative to the valve element  140  such that fluid communication between the bulk fluid container line  22  and the syringe  12  is blocked. Further, in the intermediate stop position illustrated in  FIG.  19   , fluid communication between the syringe  12  and the fluid path length  135  through the second port  20  is prevented. In addition or alternatively to stopping fluid communication between the syringe  12  and the fluid path length  135  through the second port  20 , fluid communication between the fluid path length  135  and the patient line  55  through third port  30  and/or the fourth port  40  may also be prevented. The intermediate stop position illustrated in  FIG.  19    allows for all fluid communication within the high-pressure linear stopcock  110  to be ceased without having to transition through another position, such as the fill position or the delivery position. In certain embodiments, the intermediate stop position may be used to prevent pressurized backflow of fluid from a second syringe into the high-pressure linear stopcock  110  and the syringe  12 . In certain embodiments, the intermediate stop position may allow pre-pressurization of a medical fluid in syringe  12  prior to moving the high-pressure linear stopcock  110  to the delivery position. This may have the advantage of taking up capacitance in the syringe and components and/or taking up mechanical slack in the injector system to provide a more accurate fluid delivery volume as described herein. In other embodiments, pre-pressurization of a medical fluid in syringe  12  may provide smoother pressure/flow transitions when switching between injection of a more viscous medical fluid and a less viscous medical fluid, such as contrast and saline, respectively. Examples of injection protocols using pre-pressurization to prevent fluid flow spikes during fluid transitions are described in International PCT Publication Nos. WO 2019/046260 and WO 2019/046259. In other embodiments, the intermediate stop position may allow for detection of air within the syringe system by pressurization of the syringe contents prior to the injection protocol, as described in International PCT Publication No. WO 2019/204605 entirety. In other embodiments, the intermediate stop position may allow for vacuum coalescences and purging of air bubbles from the syringe system prior to the injection protocol, as described in International PCT Publication No. WO 2019/204617. 
     Referring to  FIGS.  20  and  21   , the delivery position of the high-pressure linear stopcock  110  is illustrated according to an embodiment of the present disclosure. In the delivery position, the valve housing  130  may be slid farther in the distal direction relative to the intermediate stop position. The valve housing  130  is moved by the actuator  300  to a position relative to the valve element  140  such that fluid communication between the syringe  12  and the patient is provided through the high-pressure linear stopcock  110  and the fluid path length  135 . Further, in the delivery position, fluid communication between the bulk fluid container line  22  and the syringe  12  is blocked. Also in the delivery position illustrated in  FIGS.  20  and  21   , the first port  10  is in fluid communication with the second port  20  via the first fluid path  150 . Thus, the syringe  12  is in fluid communication with proximal end of the fluid path length  135 . In addition, the third port  30  is in fluid communication with the fourth port  40  via the second fluid path, such that the distal end of the fluid path length  135  is in fluid communication with the patient line  55 . As such, fluid injected from the syringe  12  may flow in sequence to the first port  10 , the second port  20  via the first fluid path  150 , the proximal end of the fluid path length  135  connected to the second port  20 , the third port  30  via the fluid path length  135 , the fourth port  40  via the second fluid path  160 , and finally to the patient line  55 . In the delivery position, fluid may flow from the syringe  12  to the patient fluid line  55  over the course of an injection protocol until the total desired volume of medical fluid is delivered to the patient or until at least one air bubble is detected in the upstream air detection region  120 , as described herein. In the delivery position of  FIGS.  20  and  21   , the fifth port  50 , and consequently the fluid container line  22 , are isolated from the other ports. 
     Referring now to  FIGS.  22  and  23   , the full stop position of the high-pressure linear stopcock  110  is illustrated according to an embodiment of the present disclosure. In the full stop position, the valve housing  130  may be slid to a maximum proximal position relative to the valve element  140 . In the full stop position, the valve housing  130  is moved to a position relative to the valve element  140  such that fluid communication between the fluid path length  135  through the port  30  into the patient line  55  is stopped, thereby preventing further fluid flow and potential delivery of one or more air bubbles to the patient. The valve housing  130  is moved to the full stop position by disengaging the electromechanical clutch  330  from the motor drive assembly  315 , allowing the biasing force from biasing member  310  to slide the valve housing  130  to the full stop position. As described herein, disengagement of the clutch  330  is activated by the controller  400  upon detection by the air detector  200  of at least one air bubble in the air detection region  120 . 
     Referring now to  FIGS.  24 - 26   , an embodiment of a high-pressure linear stopcock  610  that is not connected to other injector or disposable features is shown. The high-pressure linear stopcock  610  of  FIGS.  24 - 26    may be functionally similar or identical to the high-pressure linear stopcock  110  of  FIGS.  17 - 23   . However, the high-pressure linear stopcock  610  does not include the actuator  300 , the fluid path length  135 , and other fluid path components that form a part of the high-pressure linear stopcock  110 . The high-pressure linear stopcock  610  includes a valve housing  630  that is rapidly movable relative to a valve element  640 , in the same manner as the valve housing  130  and the valve element  140  of the high-pressure linear stopcock  110 . The high-pressure linear stopcock  610  includes a first port  611  configured for connection to a syringe (not shown); a second port  612  configured for connection to a proximal end of an fluid path length, such as a length of tubing (not shown); a third port  613  configured for connection to a distal end of the fluid path length; a fourth port  614  configured for connection to a patient line (not shown), and a fifth port  615  configured for connection to a bulk fluid container (not shown). The ports  611 ,  612 ,  613 ,  614 , and  615  may be arranged on the high-pressure linear stopcock  610  and may function similarly or identical to the plurality of ports  10 ,  20 ,  30 ,  40 , and  50 , respectively, of the high-pressure linear stopcock  110 . Each of ports  611 ,  612 ,  613 ,  614 , and  615  may be in the form of a connector, such as a Luer connector, a bayonet connector, or the like, to facilitate connection to their associated fluid path components. Other connector designs suitable for use on the various fluid path components are described in PCT International Application No. PCT/US2021/018523, the disclosure of which is incorporated by this reference in its entirety. 
       FIG.  25    illustrates an end-on view of the distal end of the high-pressure linear stopcock  610 , showing the fourth port  614  and the third port  613 .  FIG.  26    is a cross-section view along line C-C of  FIG.  25   . According to the illustrated embodiment, the high-pressure linear stopcock  610  is attachable to the distal end of a syringe  12  of a high-pressure fluid injector, such as shown in  FIG.  1   . In particular, the syringe  12  may be connected to the first port  611  of the high-pressure linear stopcock  610 . The high-pressure linear stopcock  610  includes an air detection region  620  at the proximal portion of the high-pressure linear stopcock  610 , analogous to the air detection region  120  of the high-pressure linear stopcock  110  and configured to be placed in operative communication with air detector  200  as described herein. 
     With continued reference to  FIGS.  25  and  26   , the valve element  640  of the high-pressure linear stopcock  610  may be substantially identical to the valve element  140  of the high-pressure linear stopcock  110 . In particular, the valve element  640  may define a first fluid path  650  and a second fluid path  660  that provide selective fluid communication between the ports  611 ,  612 ,  613 ,  614 , and  615 . One or more O-rings  616  provide a fluid tight seal between the valve element  640  and the valve housing  630  while allowing the valve housing  630  to slide relative to the valve element  640 . In certain embodiments, the valve housing  630  may slide whereas the valve element  640  is held substantially stationary. As the outer housing  130  slides relative to the valve element  640 , the high-pressure linear stopcock  110  moves between the fill position, the intermediate stop position, the delivery position, and the full stop position in essentially the same manner as the high-pressure linear stopcock  110  of  FIGS.  17 - 23   . In other embodiments, the valve element  640  may slide whereas the valve housing  630  is held substantially stationary. 
     The high-pressure linear stopcock  610  may be activated by an actuator  300  in operative communication with a controller  400  in the same manner described in connection with the high-pressure linear stopcock  610 . That is, the high-pressure linear stopcock  610  is operated by an actuator  300  and a biasing member  310 , such as a valve spring, which is biased to the full stop position but can be held one in any of the fill position, the delivery position, or the intermediate stop position by the actuator  300 . Disengaging an electromechanical clutch  330  from a motor drive assembly  315  of the actuator releases the biasing member  310  which then rapidly moves the high-pressure linear stopcock  610  to the full stop position, shutting off fluid flow from the fluid path length  135  and the patient line  55 . 
       FIGS.  27  and  28    illustrate an embodiment of the high-pressure linear stopcock  110  similar to that of  FIGS.  17  to  26   , but in which the fluid path length  135  at least partially circumferentially surrounds the valve housing  130 . As many of the components and the functionality of the embodiment of  FIGS.  27 - 28    are similar or identical to the embodiment of  FIGS.  17 - 26   , only the differences will be discussed below. As shown in  FIGS.  27  and  28   , the fluid path length  135  may be a fluid path element  720  having a cylindrical zig-zag fluid path  730 . The fluid path element  720  may be configured to surround the valve housing  130  in a cylindrical manner or other shape, such as a rectangular box-like structure, conical arrangement, etc. The fluid path  730  of the fluid path element  720  may be a zig-zag fluid path having a plurality of substantially longitudinal fluid channels  755  arranged about the valve housing  130  and a plurality of bent fluid channels  765  connecting the plurality of longitudinal fluid channels  755  in series. The plurality of longitudinal fluid channels  755  may be arranged in a tubing bundle  750  formed of a single, integral unit or multiple sections. The plurality of bent fluid channels  765  may be in the form of two end caps  760  applied to opposite ends of the bundle  750  of the longitudinal fluid channels  755 , such that each of the bend fluid channels  765  provides fluid communication between two adjacent longitudinal fluid channels  755 . Each of the bent fluid channels  765  may include up to a 180 degree turn to facilitate connection of the longitudinal fluid channels  755 . In various embodiments, the two end caps  760  may be configured to be bonded to opposite open ends of the tubing bundle  750 . According to various embodiments, each of the bent fluid channels  765  may direct fluid flow from an end of one of the longitudinal fluid channels  755  to an adjacent longitudinal fluid channel  755  of the bundle  750 , creating the cylindrical zig-zag fluid path  730 . Each end cap  760  may be bonded to opposite ends of the tubing portion  750 , for example, by adhesion, welding, solvent welding, laser welding, and the like. In certain embodiments, the plurality of longitudinal fluid channels  755  of the fluid path element  720  may be substantially straight and parallel to one another, whereas in other embodiments, the longitudinal fluid channels  755  may be in a configuration that is not parallel but nevertheless reduces the overall footprint of the fluid path element  720 . 
     Referring now to  FIG.  29   , in another embodiment, the fluid path length  135  may be a hollow cylinder  770  wrapped around the valve housing  130  and defining an internal chamber  772 . A cross section of the internal chamber  772  may be annular or ring shaped with the valve housing  130  extending through the center of the internal chamber  772 . The internal chamber  772  may be in fluid communication with the second port  20  and the third port  30 , in essentially the same manner as the tubing bindle  750  of  FIGS.  27 - 28   . The internal chamber  772  may have a total volume greater than a volume that an air bubble can travel or expand in the actuation time of the high pressure linear stopcock  110 . In some embodiments, the internal chamber  772  may have a total volume of between approximately 2.8 mL and approximately 3.6 mL, and in specific embodiments approximately 3.2 mL. Air bubbles detected by air detector  200  in the air detection region  120  are thus contained in the internal chamber  772  while the high pressure linear stopcock  110  is actuated from the delivery position to the full stop position (or to the intermediate stop position), thereby preventing the air bubbles from reaching the third port  30  and being injected into the patient. 
     As described herein, in various embodiments, the total volume and/or or length of the fluid path length  135  may be a length calculated to ensure that an air bubble detected by the air detector  200  cannot flow or expand through the entirety of the fluid path length  135  in the actuation time taken by high-pressure linear stopcock  110  to reach the stop position. As such, in certain embodiments, the total length of tubing of the fluid path  730 , including all of the longitudinal fluid channels  755  and the bent fluid channels  765 , may be from approximately 1000 millimeters to approximately 1400 millimeters and in specific embodiments may be approximately 1200 millimeters (or from approximately 3.5 to approximately 4.5 feet and in specific embodiments, may be approximately 4 feet). 
     The various fluid path tubing elements according to the various embodiments described herein may be configured to further reduce a footprint of the tubing between the air bubble sensing region  120  and valve element, for example to reduce the space occupied the tubing in an injection suit, reduce packaging size, increase ease of handling, reduce disposal volume, increase ease of manufacture, etc. while still providing sufficient volume and length to allow actuation of the valve element and prevent further flow of an air bubble into a patient after an upstream air detection event. 
     While various examples of the present invention were provided in the foregoing description, those skilled in the art may make modifications and alterations to these examples without departing from the scope and spirit of the disclosure. Accordingly, the foregoing description is intended to be illustrative rather than restrictive. The disclosure described hereinabove is defined by the appended claims, and all changes to the disclosure that fall within the meaning and the range of equivalency of the claims are to be embraced within their scope.