A flap valve magnetorheological micropump

Abstract

Various implementations include a fluid delivery device, including: a fluid chamber having a first end and a second end, the fluid chamber partially defined by a first one-way valve at the first end, a second one-way valve at the second end, a first wall including a magnetorheological elastomer, and a second wall opposite from the first wall; and an electromagnetic actuator disposed adjacent to the fluid chamber and configured to apply a magnetic field; wherein the fluid chamber is movable between a first configuration and a second configuration, wherein, upon application of the magnetic field, (i) the first wall deforms towards an interior of the fluid chamber, (ii) the first one-way valve closes, and (iii) the second one-way valve opens, placing the fluid chamber in the second configuration while moving a fluid in a flow direction from the first end to the second end and out of the fluid chamber.

Description

Attorney Docket Number: 10485-013WO1 A FLAP VALVE MAGNETORHEOLOGICAL MICROPUMP CROSS-REFERENCE TO RELATED APPLICATIONS

[0001] This application claims priority to U.S. Provisional Application No.63 / 463,060 filed April 30, 2023, which is incorporated herein by reference in its entirety. BACKGROUND

[0002] Micropumps and microfluidic devices have a wide range of applications including point-of-care and lab-on-a-chip industries. For example, insulin dosing systems provide for controlled fluid flow or medication delivery from a wearable device. However, many existing microfluidic chips are equipped with bulky supply systems that are connected with micro-bore tubing to provide air pressure or reagent. Although such systems provide precision pumping capabilities, the increased complexity hinders their applications in specific industries and populations where portable, wearable, and patchable insulin delivery systems could be utilized to enhance the well-being of type 1 diabetic patients.

[0003] Various other micropump designs, such as piezoelectric pumps, have been used in microfluidic applications. The lead zirconate titanate (PZT)-based micropumps offer a precise volumetric flow rate of aqueous fluids at fast response times and high actuation forces. However, they are complex to manufacture, require special care when installing their intricate components such as the PZT discs and demand high actuation voltages to operate.

[0004] Therefore, a need exists for a reliable, wirelessly controlled, wearable, precision micropump and medication delivery system. SUMMARY

[0005] Various implementations include a fluid delivery device, including: a fluid chamber having a first end and a second end, the fluid chamber partially defined by a first one- way valve at the first end, a second one-way valve at the second end, a first wall including a magnetorheological elastomer, and a second wall opposite from the first wall; and an electromagnetic actuator disposed adjacent to the fluid chamber and configured to apply a magnetic field; wherein the fluid chamber is movable between a first configuration and a second configuration, wherein, upon application of the magnetic field, (i) the first wall deforms towards an interior of the fluid chamber, (ii) the first one-way valve closes, and (iii) the second one-way valve opens, placing the fluid chamber in the second configuration while moving a fluid in a flow direction from the first end to the second end and out of the fluid chamber.Attorney Docket Number: 10485-013WO1

[0006] In some implementations, a fluid delivery device, wherein each of the first one- way valve and the second one-way valve includes: a flap valve protrusion extending a first distance from the first wall into the interior of the fluid chamber along a first axis, the first axis being substantially perpendicular to the first wall; and a base support extending a second distance from the second wall into the interior of the fluid chamber along a second axis, the second axis being substantially parallel to the first axis, the first axis being offset from the second axis along the flow direction closer to the second end; wherein, in the first configuration, the distance between the first wall and the second wall is less than the sum of the first distance and the second distance such that the flap protrusion and the base support overlap to define a gap.

[0007] In some implementations, a fluid delivery device, wherein, in the second configuration, the flap valve protrusion of the first one-way valve moves towards the base support of the first one-way valve to close the gap of the first one-way valve; and the flap valve protrusion of the second one-way valve moves away from the base support of the second one-way valve to extend the gap of the second one-way valve.

[0008] In some implementations, a fluid delivery device, where each of the first one- way valve and the second one-way valve are duckbill valves.

[0009] In some implementations, a fluid delivery device, where each of the first one- way valve and the second one-way valve includes: a first protrusion integrally coupled to the first wall, the first protrusion including: a first connector portion coupled to and extending out from the first wall; a first contoured portion coupled to the connector portion, the contoured portion extending (i) along the flow direction from the first end towards the second end of the fluid chamber and (ii) at least partially towards the second wall at an angle with respect to the flow direction; and a first valve tip coupled to the contoured portion, the valve tip extending along the flow direction; and a second protrusion coupled to the second wall immediately opposite the first protrusion; wherein the second protrusion is substantially similar to the first protrusion such that the first valve tip is disposed adjacent and parallel to a second valve tip of the second protrusion, the first valve tip and the second valve tip defining a gap.

[0010] In some implementations, a fluid delivery device, wherein, in the second configuration, the first and second valve tips of the first one-way valve move towards each other to close the gap of first one-way valve; and the first and second valve tips of the second one-way valve move away from each other to extend the gap of the second one-way valve.Attorney Docket Number: 10485-013WO1

[0011] In some implementations, a fluid delivery device, further including a third one- way valve, wherein the fluid chamber is a first fluid chamber, the second and third one-way valves defining a second fluid chamber disposed further along the flow direction with respect to the first fluid chamber; and a second electromagnetic actuator disposed adjacent to the second fluid chamber.

[0012] In some implementations, a fluid delivery device, wherein the first electromagnetic actuator is configured to apply a first magnetic field to move the first fluid chamber from the first configuration to the second configuration; wherein, after the first magnetic field is applied, the first magnetic field is removed and the second electromagnetic actuator applies a second magnetic field to move the second fluid chamber from the first configuration to the second configuration, moving fluid from the first fluid chamber to the second fluid chamber.

[0013] In some implementations, a fluid delivery device further including a plurality of one-way valves defining a plurality of fluid chambers with a corresponding plurality of electromagnetic actuators, wherein a plurality of magnetic fields are applied and removed sequentially to (i) move each of the plurality of fluid chambers between a first and second configuration, and (ii) move fluid between the plurality of fluid chambers along the flow direction.

[0014] In some implementations, a fluid delivery device, wherein the first and second one-way valves and the second wall include a base matrix (e.g., silicon), wherein magnetorheological elastomer of the first wall includes a base matrix (e.g., silicon) and micro- or nano-sized ferromagnetic iron particles embedded within the base matrix.

[0015] In some implementations, a fluid delivery device, where the first wall includes polydimethylsiloxane (PDMS).

[0016] In some implementations, a fluid delivery device, wherein the magnetorheological elastomer is isotropic or non-isotropic.

[0017] In some implementations, a fluid delivery device, wherein the fluid is a medication.

[0018] In some implementations, the fluid delivery device further includes at least one side wall extending between the first wall and the second wall, the at least one side wall further defining the fluid chamber.

[0019] In some implementations, a system including: a plurality of fluid delivery devices, each device including: a fluid chamber having a first end and a second end, the fluidAttorney Docket Number: 10485-013WO1 chamber partially defined by a first one-way valve at the first end, a second one-way valve at the second end, a first wall including a magnetorheological elastomer, and a second wall opposite from the first wall, wherein the fluid chamber is movable between a first configuration and a second configuration; a plurality of electromagnetic actuators disposed adjacent to each of the fluid chambers of the plurality of fluid delivery devices, each electromagnetic actuator being configured to apply a magnetic field to deform the first wall towards the interior of the fluid chamber, close the first one-way valve, and open the second one-way valve, moving fluid in the flow direction; and a control system in electrical communication with each of the plurality of electromagnetic actuators, the control system configured to actuate the plurality of electromagnetic actuators in a pre-defined sequence to move fluid from one end of the plurality of fluid delivery devices to a second end of the plurality of fluid delivery devices.

[0020] Various implementations include a method of fabricating a device described herein. In some implementations, a method of fabricating a fluid delivery device having a valve system and a magnetorheological elastomer, the method including: 3D printing the valve system using a base material; and 3D printing the magnetorheological elastomer on a first wall of the fluid delivery device, the magnetorheological elastomer being integrally formed with the base material of the valve system. BRIEF DESCRIPTION OF DRAWINGS

[0021] Example features and implementations of the present disclosure are disclosed in the accompanying drawings. However, the present disclosure is not limited to the precise arrangements and instrumentalities shown. Similar elements in different implementations are designated using the same reference numerals.

[0022] FIG.1A shows model of a fluid delivery device with flap valves, according to one implementation.

[0023] FIG.1B shows a front view of the model of FIG.1A, according to one implementation.

[0024] FIG.1C shows a diagram of the fluid delivery device of FIG.1A, according to one implementation.

[0025] FIG.1D shows the diagram of FIG.1C with example measurements, according to one implementation.

[0026] FIG.1E shows an example assembly for the fluid delivery device of FIG.1A, according to one implementation.Attorney Docket Number: 10485-013WO1

[0027] FIG.2A shows model of a fluid delivery device with duckbill valves, according to one implementation.

[0028] FIG.2B shows a front view of the model of FIG.1A, according to one implementation.

[0029] FIG.2C shows a diagram of the fluid delivery device of FIG.1A, according to one implementation.

[0030] FIG.2D shows the diagram of FIG.1C with example measurements, according to one implementation.

[0031] FIG.3A shows a diagram of a system including a control system and a model of a fluid delivery device including a plurality of one-way valves, according to one implementation.

[0032] FIG.3B shows a perspective view of the model of the fluid delivery device of FIG.3A, according to one implementation.

[0033] FIG.4A shows an exploded view of an example wearable patch, according to one implementation.

[0034] FIG.4B shows the wearable patch of FIG.4A in an assembled configuration, according to one implementation.

[0035] FIG.5 shows a flowchart of the simulation process in COMSOL, according to one implementation.

[0036] FIGS.6A-6C show a device model with the main components and dimensions for the simulation, according to one implementation.

[0037] FIG.7 shows a table of the comparisons between the benchmark study and this study, according to one implementation.

[0038] FIG.8 presents a comparison graph for height of the pump chamber and flow rate for this study and a benchmark study, according to one implementation.

[0039] FIG.9A is a graph demonstrating the magnetic flux density acting on the upper wall across the length of the microchannel, according to one implementation.

[0040] FIG.9B is a graph of the deformation of the upper MRE wall, under the influence of magnetic field, according to one implementation.

[0041] FIG.10A is a graph showing the velocity field inside the pump at t = 0.1 s when the maximum velocity occurs, while FIG.10B shows the variation of total volume flow rate with time, according to one implementation.Attorney Docket Number: 10485-013WO1

[0042] FIG.11A shows the results of a simulation wherein one-way flap valves were added inside the pump chamber, according to one implementation. FIG.11B shows a graph of flow rate over time for the simulation in FIG.11A.

[0043] FIG.12A shows the results of a simulation wherein a duckbill flap valve was added inside the pump chamber, according to one implementation. FIG.12B shows a graph of flow rate over time for the simulation in FIG.12A.

[0044] FIGS.13 and 14 show the volume flow rate during both contraction and retraction phases for (a) without valves and (b) with the flap valves, according to one implementation.

[0045] FIGS.15A-15F show the displacement and velocity field history of the micropump for the contraction phase, i.e., t = 0 - 0.5 s, according to one implementation.

[0046] FIG.16 shows the time history of net volume transferred through the right terminal of the micropump, according to one implementation.

[0047] FIGS.17A-F show the displacement and velocity field history of the micropump for the contraction phase, i.e., t = 0 - 0.5 s, according to one implementation.

[0048] FIG.18 shows the time history of net volume transferred through the right terminal of the micropump, according to one implementation.

[0049] FIG.19A is a graph showing that the net pumped volume is increasing with the height of the pump chamber for a flap valve design, according to one implementation.

[0050] FIG.19B is a graph showing that the net pumped volume increases with the height of the pump chamber, for a duckbill valve, according to one implementation.

[0051] FIG.20A is a graph showing the variation of the net pump volume with respect to the thickness of the upper wall for a flap valve design, according to one implementation.

[0052] FIG.20B is a graph showing the variation of the net pump volume with respect to the thickness of the upper wall for a duckbill valve, according to one implementation.

[0053] FIG.21A is a graph showing the effect of the elastic modulus of the pump material on the net pumped volume for a flap valve design, according to one implementation.

[0054] FIG.21B is a graph showing the effect of elastic modulus of the pump material on the net pumped volume for a duckbill valve, according to one implementation.

[0055] FIG.22A is a graph showing the influence of valve spacing distance on the net pumped volume, for a flap valve design, according to one implementation.

[0056] FIG.22B is a graph showing the influence of valve spacing distance on the net pumped volume for a duckbill valve, according to one implementation.Attorney Docket Number: 10485-013WO1

[0057] FIG.23A is a graph showing the effect of the Poisson's ratio of the valves for a flap valve design, according to one implementation.

[0058] FIG.23B is a graph showing the effect of Poisson's ratio on the valves for a duckbill valve, according to one implementation.

[0059] FIG.24A is a graph showing the effect of valve height on the net pumped volume for a flap valve design, according to one implementation.

[0060] FIG.24B is a graph showing the influence of the upper wall's Poisson's ratio on the net pumped volume for a duckbill valve, according to one implementation.

[0061] FIG.25A is a graph showing the effect of valve width on the net pumped volume for a flap valve design, according to one implementation.

[0062] FIG.25B is a graph showing the effect of the valve length on the pumping performance in terms of the net pumped volume for a duckbill valve design, according to one implementation.

[0063] FIG.26A shows a schematic diagram of the developed experimental setup, according to one implementation.

[0064] FIG.26B shows a picture of the 3D printed micropump prototype.

[0065] FIG.26C is a picture of the experimental setup shown in FIG.26A.

[0066] FIG.27 is a diagram showing the maximum magnetic flux that occurs at 0.5 second for a described study.

[0067] FIG.28A shows a graph of the equivalent variation in magnetic flux over time, according to one implementation.

[0068] FIG.28B shows a graph of total magnetic energy over time, according to one implementation.

[0069] FIG.29 shows a diagram of the example device model depicting the stress applied to the upper wall because of the magnetic field, according to one implementation.

[0070] FIG.30 shows a graph of variations in stress on the upper wall throughout the actuation cycle, according to one implementation.

[0071] FIG.31 shows a model of the deformation of the upper wall of the model device resulting from stress, according to one implementation.

[0072] FIG.32 shows a graph of displacement over time for the upper wall of the model, according to one implementation.

[0073] FIG.33 shows a velocity field in the model device induced by deformation of the upper wall, according to one implementation.Attorney Docket Number: 10485-013WO1

[0074] FIG.34 shows a graph of mass flow rate over time.

[0075] FIG.35 shows a graph of net pumped volume over time, each for the study of FIG.33, according to one implementation.

[0076] Various objects, aspects, features, and advantages of the disclosure will become more apparent and better understood by referring to the detailed description taken in conjunction with the accompanying drawings, in which like reference characters identify corresponding elements throughout. In the drawings, like reference numbers generally indicate identical, functionally similar, and / or structurally similar elements. DETAILED DESCRIPTION

[0077] The devices, systems, and methods disclosed herein provide for fluid delivery via an electro-mechanical micropump. The devices, systems, and methods described herein provide for micropumps utilizing magnetorheological material and electromagnets to controllably deform a membrane of a fluid chamber. Mechanical deformation of the membrane may be accomplished by application of a magnetic field. Based on the geometry of the fluid chamber, the mechanical deformation displaces a volume of fluid (e.g., a medication) out of the fluid chamber (e.g., and into a patient).

[0078] The membrane may be a magnetorheological elastomer (MRE) – a composite material consisting of a rubber-like base material (e.g., silicon) and micron-sized iron particles doped in it. For example, the membrane may include a ferromagnetic composite material such as a Polydimethylsiloxane (PDMS) base matrix with micro- or nano-sized ferromagnetic iron particles embedded therein. While a portion of the membrane may include a MRE, the remainder may comprise a passive elastomer. MREs can be designed as isotropic and non- isotropic, meaning that the magnetic iron particles inside them can be aligned in special configurations so the material responds to the applied loads differently.

[0079] The geometry of the fluid chamber includes a variety of designs dependent upon the desired use-case. While some designs feature a ferromagnetic membrane that deflects into a disk-shaped reservoir to generate the pumping effect, others contract a circular or rectangular flow channel for a pulsated flow. Using a magnetic field as a trigger has several advantages over other modes of operation. Magnetic actuators can generate strong force and displacement with lower power consumption, and they are less prone to electrical heat loss and high-voltage failure. Moreover, the actuation parts and magnetic field generating parts can be physically separated, so these systems do not require complex wiring.Attorney Docket Number: 10485-013WO1

[0080] While fabrication of certain magnetorheological elastomer fluid pumps have been challenging in the past, this disclosure provides for methods of manufacturing such devices. Advances in 3D printing technology provide for accurate and consistent manufacture of magnetorheological micropumps. The systems, devices, and methods of this disclosure provide for magnetorheological micropumps that are miniature (e.g., on the order of 1 mm), lightweight, portable, wirelessly controllable (e.g., with a fast response time of less than 100 ms), durable, and low power consuming. The systems, devices, and methods of this disclosure can be implemented into, for example, a wearable medication delivery device having a small footprint. Example System #1 – Flap Valve

[0081] FIGS.1A – 1D show a fluid delivery device 100 including a fluid chamber 102 and an electromagnetic actuator 150 disposed adjacent to the fluidic chamber 102. The fluid chamber 102 has a first end 104 and a second end 106 opposite from the first end 104. The fluid chamber 102 is partially defined by a first one-way valve 120 at the first end 104 and a second one-way valve 130 at the second end 106. The fluid chamber 102 is further defined in part by a first wall 108 and a second wall 110 opposite from the first wall 108, the first wall 108 comprising a magnetorheological elastomer. Each of the first wall 108 and the second wall 110 extend between the first one-way valve 120 and the second one-way valve 130. The fluid chamber 102 is further defined by at least one side wall 160 extending between the first wall 108 and the second wall 110. FIGS.1A and 1B provide cutaway views of the fluid delivery device 100; therefore, only a first side wall 160 is shown. However, the fluid delivery device 100 can be sealed via a second side wall on the opposite side of the first side wall 160. The fluid chamber 102 has a flow direction 112 from the first end 104 to the second end 106, illustrated by the arrow shown in the fluid chamber 102.

[0082] The fluid chamber 102 is movable between a first configuration (shown in FIGS.1C and 1D) and a second configuration (shown in FIGS.1A and 1B). The distance between at least a portion of the first wall 108 and at least a portion of the second wall 110 (shown as distance “H” in FIG.1D) in the first configuration is greater than the distance between at least a portion of the first wall 108 and at least a portion of the second wall 110 in the second configuration.

[0083] Each of the first one-way valve 120 and the second one-way valve 130 of fluid delivery device 100 are flap valves and are nearly identical in structure. Each of the first one-Attorney Docket Number: 10485-013WO1 way valve 120 and the second one-way valve 130 of fluid delivery device 100 are disposed along fluid delivery device 100 spaced apart from each other along the flow direction 112.

[0084] The first one-way valve 120 includes a flap protrusion 122 extending a first distance (e.g., distance “h” in FIG.1D) from the first wall 108 into the interior of the fluid chamber 102 along a first axis 124. The first axis 124 is substantially perpendicular to the first wall 108. The first one-way valve 120 further includes a base support 126 extending a second distance from the second wall 110 into the interior of the fluid chamber 102 along a second axis 128. The second axis 128 is substantially parallel to the first axis 124. The first axis 124 is offset from the second axis 128 along the flow direction 112, the first axis 124 being closer to the second end 106.

[0085] In the first configuration, the flap protrusion 122 and the base support 126 overlap to define a gap 129. In other words, the distance between the first wall 108 and the second wall 110 in the first configuration is less than the sum of the first distance (the extension of the flap protrusion 122) and the second distance (the extension of the base support 126). Thus, the gap 129 provides a fluid entry point on the first end 104 of the fluid chamber 102. Fluid flow through the gap 129 is transverse to the flow direction 112.

[0086] The second one-way valve 130 also includes a flap protrusion 132 extending a first distance (e.g., distance “h” in FIG.1D) from the first wall 108 into the interior of the fluid chamber 102 along a first axis 134. The first axis 134 is substantially perpendicular to the first wall 108. The second one-way valve 130 further includes a base support 136 extending a second distance from the second wall 110 into the interior of the fluid chamber 102 along a second axis 138. The second axis 138 is substantially parallel to the first axis 134. The first axis 134 is offset from the second axis 138 along the flow direction 112, the first axis 134 being closer to the second end 106.

[0087] In the first configuration, the flap protrusion 132 and the base support 136 overlap to define a gap 139. In other words, the distance between the first wall 108 and the second wall 110 in the first configuration is less than the sum of the first distance (the extension of the flap protrusion 132) and the second distance (the extension of the base support 136). Thus, the gap 139 provides a fluid exit point on the second end 106 of the fluid chamber 102. Fluid flow through the gap 139 is transverse to the flow direction 112.

[0088] In use, the electromagnetic actuator 150 is configured to apply a magnetic field 152. The field lines for the magnetic field 152 are depicted in FIGS.1A and 1B to illustrate the operation of the fluid delivery device 100. Upon activation of the electromagnetic actuator 150,Attorney Docket Number: 10485-013WO1 the first wall 108 having the magnetorheological elastomer is pulled by the magnetic field 152. The first wall 108 deforms towards the interior of the fluid chamber 102.

[0089] As the first wall 108 deforms, the first one-way valve 120 closes and the second one-way valve 130 opens, placing the fluid chamber 102 in the second configuration. In the second configuration, the distance between at least a portion of the first wall 108 (e.g., the midpoint between the first one-way valve 120 and the second one-way valve 130) and at least a portion of the second wall 110 is less than the same distance in the first configuration. Thus, the volume inside the fluid chamber 102 is reduced in the second configuration.

[0090] Movement of the fluid chamber 102 from the first configuration to the second configuration moves a fluid in the flow direction 112 from the first end 104 to the second end 106 and out of the fluid chamber 102. For example, movement of the fluid chamber 102 from the first configuration to the second configuration moves a fluid medication or therapeutic out of the fluid chamber 102 and into a delivery tube and / or a patient.

[0091] As the first wall 108 deforms, the flap protrusion 122 of the first one-way valve 120 and changes orientation with respect to the first axis 124. The flap protrusion 122 is directed or angled backwards towards the base support 126 (i.e., opposite of the flow direction 112) to close the gap 129. Thus, in the second configuration, the first one-way valve 120 is closed.

[0092] As the first wall 108 deforms, the flap protrusion 132 of the second one-way valve 130 changes orientation with respect to the first axis 134. The flap protrusion 132 is directed or angled forwards away from the base support 136 (i.e., along the flow direction 112) to open the gap 139. Thus, in the second configuration, the second one-way valve 130 is open.

[0093] Further disclosed herein is a method of fabricating the fluid delivery device 100 or a similar fluid delivery device having a valve system and a magnetorheological elastomer. The method includes 3D printing the valve system using a base material. The method further includes 3D printing the magnetorheological elastomer on a first wall of the fluid delivery system (e.g., first wall 108) wherein the magnetorheological elastomer is integrally formed with the base material of the valve system.

[0094] FIG.1E shows an example assembly of a fluid delivery device (e.g., the fluid delivery device 100 of this example), according to one implementation. The assembly includes an upper wall of the chamber made of silicone that is attached with a semi-active smart magnetorheological elastomer (MRE) sheet. The rest of the wall is made of a passive elastomer. A permanent magnet is placed just below the device.Attorney Docket Number: 10485-013WO1 Example System #2 – Duckbill Valve

[0095] FIGS.2A – 2D show a fluid delivery device 200 including a fluid chamber 202 and an electromagnetic actuator 150 disposed adjacent to the fluidic chamber 202. The fluid delivery device 200 and the fluid chamber 202 are substantially similar to the fluid delivery device 100 and the fluid chamber 102 of FIGS.1A – 1D; however, the first and second one- way valves in the fluid delivery device 200 are different than those of the fluid delivery device 100.

[0096] The fluid chamber 202 is partially defined by a first one-way valve 220 at the first end 104 and a second one-way valve 230 at the second end 106. The fluid chamber 202 is further defined in part by a first wall 108 and a second wall 110 opposite from the first wall 108, the first wall 108 comprising a magnetorheological elastomer. Each of the first wall 108 and the second wall 110 extend between the first one-way valve 220 and the second one-way valve 230. The fluid chamber 202 is further defined by at least one side wall 160 extending between the first wall 108 and the second wall 110. FIGS.2A and 2B provide cutaway views of the fluid delivery device 200; therefore, only a first side wall 160 is shown. However, the fluid delivery device 200 can be sealed via a second side wall on the opposite side of the first side wall 160.

[0097] Each of the first one-way valve 220 and the second one-way valve 230 of fluid delivery device 200 are duckbill valves and are nearly identical in structure. Each of the first one-way valve 220 and the second one-way valve 230 of fluid delivery device 200 are disposed along fluid delivery device 200 spaced apart from each other along the flow direction 112.

[0098] The first one-way valve 220 includes a first protrusion 222 integrally coupled to the first wall 108. The first protrusion 222 comprises a first connector portion 224, a first contoured portion 226, and a first valve tip 228. The first connector portion 224 is coupled to and extends out from the first wall 108. The first contoured portion 226 is coupled to the connector portion 224. The contoured portion 226 extends along the flow direction 112 from the first end 104 towards the second end 106 of the fluid chamber 202. The contoured portion 226 extends at least partially towards the second wall 110 at an angle with respect to the flow direction 112. The first valve tip 228 is coupled to the contoured portion 226. The first valve tip 228 extends along the flow direction 112.

[0099] The first one-way valve 220 further includes a second protrusion 242 coupled to the second wall 110 immediately opposite from the first protrusion 222. The second protrusionAttorney Docket Number: 10485-013WO1 242 is substantially similar to the first protrusion 222 such that the first valve tip 228 is disposed adjacent and parallel to a second valve tip 248 of the second protrusion 242. The first valve tip 228 and the second valve tip 248 define a gap 229. The gap 229 provides a fluid entry point on the first end 104 of the fluid chamber 202.

[0100] The second one-way valve 230 includes a first protrusion 232 integrally coupled to the first wall 108. The first protrusion 232 comprises a first connector portion 234, a first contoured portion 236, and a first valve tip 238. The first connector portion 234 is coupled to and extends out from the first wall 108. The first contoured portion 236 is coupled to the connector portion 234. The contoured portion 236 extends along the flow direction 112 from the first end 104 towards the second end 106 of the fluid chamber 202. The contoured portion 236 extends at least partially towards the second wall 110 at an angle with respect to the flow direction 112. The first valve tip 238 is coupled to the contoured portion 236. The first valve tip 238 extends along the flow direction 112.

[0101] The second one-way valve 230 further includes a second protrusion 252 coupled to the second wall 110 immediately opposite from the first protrusion 232. The second protrusion 252 is substantially similar to the first protrusion 232 such that the first valve tip 238 is disposed adjacent and parallel to a second valve tip 258 of the second protrusion 252. The first valve tip 238 and the second valve tip 258 define a gap 239. The gap 239 provides a fluid exit point on the second end 106 of the fluid chamber 202.

[0102] Similar to the fluid chamber 102, the fluid chamber 202 of fluid delivery device 200 is movable between a first configuration (shown in FIGS.2C and 2D) and a second configuration (shown in FIGS.2A and 2B). The distance between at least a portion of the first wall 108 and at least a portion of the second wall 110 (shown as distance “H” in FIG.2D) in the first configuration is greater than the distance between at least a portion of the first wall 108 and at least a portion of the second wall 110 in the second configuration.

[0103] In use, the electromagnetic actuator 150 is configured to apply a magnetic field 152, similar to that of fluid delivery device 100. Thus, the first wall 108 deforms towards the interior of the fluid chamber 202. As the first wall 108 deforms, the first one-way valve 220 closes and the second one-way valve 230 opens, placing the fluid chamber 202 in the second configuration wherein the volume of the fluid chamber 202 is reduced. Movement of the fluid chamber 102 from the first configuration to the second configuration moves a fluid in the flow direction 112 from the first end 104 to the second end 106 and out of the fluid chamber 102. For example, movement of the fluid chamber 102 from the first configuration to the secondAttorney Docket Number: 10485-013WO1 configuration moves a fluid medication or therapeutic out of the fluid chamber 102 and into a delivery tube and / or a patient.

[0104] As the first wall 108 deforms, the pressure in the fluid chamber 202 increases, forcing fluid through the first one-way valve 220. The first valve tip 228 of the first protrusion 222 and the second valve tip 248 of the second protrusion 242 are forced apart, increasing the distance between the first valve tip 228 and the second valve tip 248. Thus, the gap 229 is larger in the second configuration, allowing fluid to flow out of the fluid chamber 202.

[0105] Simultaneously, the second one-way valve 230 experiences backpressure and closes. The first valve tip 238 of the first protrusion 232 and the second valve tip 258 of the second protrusion 252 are forced together. Thus, the gap 239 is smaller or closed in the second configuration, preventing fluid from flowing into the fluid chamber 202. Example System #3 – Multi-Valve Device and System

[0106] FIGS.3A and 3B show a fluid delivery device 300 including a plurality of one- way valves partially defining a plurality of fluid chambers and a plurality of electromagnetic actuators disposed adjacent to one of the plurality of fluid chambers. The fluid delivery device 300 is similar to fluid delivery device 200 except that fluid delivery device 300 includes multiple fluid chambers and more than two one-way valves. Each of the one-way valves, fluid chambers, and electromagnetic actuators shown have similar structure and function as those in fluid delivery device 200. In other words, fluid delivery device 300 includes a series of duckbill valves arranged in series. However, in other implementations, the fluid delivery device 300 could include a series of flap valves as in fluid delivery device 100.

[0107] Fluid delivery device 300 includes four one-way valves: first one-way valve 302, second one-way valve 304, third one-way valve 306, and fourth one-way valve 308. The first one-way valve 302 and the second one-way valve 304 partially define a first fluid chamber 310. The second one-way valve 304 and the third one-way valve 306 partially define a second fluid chamber 312. The third one-way valve 306 and the fourth one-way valve 308 partially define a third fluid chamber 314. Each of the fluid chambers 310, 312, 314 include a first wall 316 comprising a magnetorheological elastomer and a second wall 318 opposite the first wall 316. A first electromagnetic actuator 320 is disposed adjacent to the first fluid chamber 310. A second electromagnetic actuator 322 is disposed adjacent to the second fluid chamber 312. A third electromagnetic actuator 324 is disposed adjacent to the third fluid chamber 314.Attorney Docket Number: 10485-013WO1

[0108] The fluid delivery device 300 includes a common flow direction 326. Each of the fluid chambers are movable between a first and second configuration, similar to that of fluid delivery device 200. As shown, the third fluid chamber 314 is further along the flow direction 326 than the second fluid chamber 312, which is further long the flow direction 326 than the first fluid chamber 310.

[0109] The first electromagnetic actuator 320 is configured to apply a first magnetic field (not shown) to move the first fluid chamber 310 from the first configuration to the second configuration. After the first magnetic field is applied, the first magnetic field is removed (i.e., the first electromagnetic actuator 320 is turned off), moving the first fluid chamber 310 back to the first configuration. Then, the second electromagnetic actuator 322 is turned on. The second electromagnetic actuator 322 applies a second magnetic field 328. The field lines of the second magnetic field 328 are shown in FIGS.3A and 3B to illustrate the operation of the fluid delivery device 300. Thus, the second magnetic field 328 moves the second fluid chamber 312 from the first configuration to the second configuration, moving fluid from the first fluid chamber 310 to the second fluid chamber 312.

[0110] Similarly, the second electromagnetic actuator 322 may be turned off and the third electromagnetic actuator 324 turned on, moving the second fluid chamber 312 back to the first configuration. Then, the third fluid chamber 314 is moved from the first configuration to the second configuration, moving fluid from the second fluid chamber 312 to the third fluid chamber 314. This process is repeated for as many fluid chambers as are present in the fluid delivery device to move the fluid along the flow direction.

[0111] In some implementations, a system is disclosed comprising the fluid delivery device 300 and a control system 350, as shown in FIG.3A. The control system 350 is in electrical communication with each of the electromagnetic actuators 320, 322, and 324. The control system 350 is configured to actuate the electromagnetic actuators 320, 322, 324 in a pre-defined sequence to move fluid from the first end 104 of the fluid delivery device 300 to the second end 106 of the fluid delivery device 300 along the flow direction 326. Example System #4 – Wearable Patch Device

[0112] FIGS.4A and 4B show an example application of any of the fluid delivery devices described herein. In one implementation, the MRE micropump is integrated into a wearable patch 400 (e.g., an insulin patch) to be attached to a patient’s skin. The wearable patch 400 may be wirelessly controllable (e.g., via a smartphone app) and configured to deliver medication to a user based on preconfigured instructions or based on wireless controls.Attorney Docket Number: 10485-013WO1

[0113] The wearable patch 400 includes a housing 402 and a base plate 404 that optionally includes an adhesive capable of sticking to human skin. A MRE pump chamber 406 is disposed on the base plate 404. The MRE pump chamber 406 comprises any of the above- described implementations of a fluid delivery device (e.g., fluid delivery device 100, 200, or 300) or a separately described fluid delivery device. Electromagnets 408 are disposed adjacent to the MRE pump chamber 406. A circuit board 410 is in electrical communication with the electromagnets 408, the circuit board 410 optionally including a microcontroller configured to send instructions to activate the electromagnets 408 and / or communicate with a wireless controller (e.g., a smartphone). The circuit board 410 also includes a power unit 412.

[0114] The wearable path 400 further includes a flexible membrane 414. In use, the circuit board 410 (e.g., the microcontroller or a processor of the circuit board 410) activates the electromagnets 408 which deform a portion of the MRE pump chamber 406. The deformation pulls fluid from the flexible membrane 414 and pushes it out of the wearable patch 400. For example, the fluid (e.g., insulin) is dispensed in a controlled and metered dose into a patient’s arm. EXPERIMENTAL TESTING AND RESULTS

[0115] The following examples are set forth below to illustrate the methods and results according to the disclosed subject matter. These examples are not intended to be inclusive of all aspects of the subject matter disclosed herein, but rather to illustrate representative methods and results. These examples are not intended to exclude equivalents and variations of the present invention which are apparent to one skilled in the art. EXAMPLE #1 – Magnetorheological Flap and Duckbill Valve Micropump for Drug Delivery Applications

[0116] A multiphysics-based simulation methodology was conducted to prove the proposed concept of a flap valve micro-fluidic pump that relies on an electromagnetic actuation mechanism. More specifically, the complex and fully coupled magneto-solid-fluid interaction analyses were carried out via a two-dimensional, time-dependent computational model to determine the deformation of the upper wall of the pump chamber and the velocity field inside the pump channel. The simulations were performed in COMSOL Multiphysics software. The simulation approach was verified through a validity check study by replicating an existing study in the literature. Once verified, the full simulations were performed for the proposed concept. The performance characteristics of the pump were presented and discussed. In addition, a parametric study was conducted to see the effects of important design parametersAttorney Docket Number: 10485-013WO1 on the net pumped volume, results of which were also presented and discussed. In one implementation, the proposed micropump can transfer 1.9 µl of fluid in one pumping cycle, which is almost two times the other micropump models. Also, the proposed flap valve can reduce the backflow up to 10 times during the expansion phase in comparison with the no valve model. The parametric studies demonstrated that the net pumped volume of the fluid is directly proportional to the channel height and valve spacing distance and is inversely proportional to the upper wall thickness, elastic modulus of the pump structure, width, height, and Poisson ratio of the valves. The proposed micropump could potentially be used in a broad range of applications, such as an insulin dosing system for Type 1 Diabetic patients, artificial organs to transport blood, organ-on-chip applications, and so on.

[0117] Magnetic-based designs that rely on mechanical displacement of a membrane can be categorized into two groups: (i) designs where the membranes are pushed by a set of actuator heads to create a pressure differential and (ii) designs that deform a ferromagnetic composite material, usually consisting of a Polydimethylsiloxane (PDMS) base matrix and micro- or nano-sized ferromagnetic iron particles embedded in them, under an externally applied magnetic field. Designs from the first category are complex and have excess moving components, which could become a concern for installation and maintenance. The second category of pumps is more design-dependent. While some designs feature a ferromagnetic membrane that deflects into a disk-shaped reservoir to generate the pumping effect, others contract a circular or rectangular flow channel for a pulsated flow. Using a magnetic field as a trigger has several advantages over other modes of operation. Magnetic actuators can generate strong force and displacement with lower power consumption, and they are less prone to electrical heat loss and high-voltage failure. Moreover, the actuation parts and magnetic field generating parts can be physically separated, so these systems do not require complex wiring.

[0118] Magnetorheological elastomers (MREs) are composite materials consisting of a rubber-like base material and micron-sized iron particles doped in it. They can be designed as isotropic and non-isotropic, meaning that the magnetic iron particles inside them can be aligned in special configurations so the material responds to the applied loads differently. As such, these materials have found very wide application areas, ranging from vibration mounts in automobile engines to bearings in large building structures and bridges as well as sensor applications for structural health monitoring purposes, and many more.

[0119] Existing micropumps implementing a magnetic-based design generally fail to provide an adequate pumping solution for specific applications. For example, some pumpAttorney Docket Number: 10485-013WO1 designs (e.g., a conical valve micropump) offer lower pumping capacity. Some angle valve type micropumps suffer from large backflow during the contraction phase because of the large gap between the tip of the valves and the upper wall. Other micropump designs have a complex geometry, which could create inconveniences during fabrication. Hence, there is still need for effective MRE micropump designs that could leverage the modern manufacturing technologies.

[0120] In the light of the above discussions, this disclosure provides a novel magnetorheological peristaltic micropump which offers an efficient, miniature (on the order of 1 mm), light-weight, portable, wirelessly-controllable (with a fast response time of less than 100 ms), durable, low-power micropump for drug delivery. The proposed design is not only novel but is also designed to be fabricated by 3D printing technologies in a more convenient way than the existing MRE micropumps in literature.

[0121] A multiphysics-based simulation approach was adopted to prove the proposed concept. Highly coupled magneto-solid-fluid interaction simulations were carried out in COMSOL Multiphysics software (v5.6). To investigate the effects of significant design parameters, a parametric analysis was also conducted. Example Design

[0122] One implementation of the proposed micropump design consists of a pump chamber, two one-way flap valves, and an electromagnet (e.g., the pump of FIGS.1A and 1B). The top wall of the pump chamber is made of a semi-active smart material called magnetorheological elastomer (MRE), while the rest of the structure is made from a passive elastomer. MREs, falling in the category of composite materials, are composed of a rubber-like base matrix, such as silicon, and micron-sized iron particles embedded in it. Because of their ferromagnetic properties, the MREs deform or can be designed to resist the deformation in the presence of a magnetic field, depending on design intent. Since their mechanical properties alter by the induced magnetic field, they are properly categorized as semi-active materials. In the example proposed micropump design, under an external magnetic field, the top wall contracts towards the pumping chamber. The amount of contraction depends on the intensity of the applied magnetic field, which can be controlled via an electromagnet. The deformation on the top wall creates a squeezing effect on the fluid inside the flow chamber, pushing the fluid through the one-way valve in the front end. While this is happening, a one-way flap valve in the rear end prevents the fluid from leaking backward, thus creating an effective unidirectional pumping mechanism.Attorney Docket Number: 10485-013WO1

[0123] Another implementation of the proposed micropump design consists of a pumping chamber, two one-way duckbill valves, and an electromagnet (e.g., the pump of FIGS.2A and 2B). The top wall the pumping chamber is made from a semi-active material called magnetorheological elastomer (MRE), while the rest of the structure, including the valves, consist of a passive elastomer. MREs are categorized as composite materials as they are composed of an elastomeric (or polymeric) matrix, such as silicon, with micron-sized magnetically permeable particles, typically iron particles, doped in it. Due to their ferromagnetic properties, MREs deform under an external magnetic field. In contrast, they can also be designed to resist the deformation by activating an external magnetic field. This unique feature of MREs allowed them to be utilized in a wide range of application areas including, actuation systems, vibration isolation systems, and sensors. In the example designs described herein, the top wall contracts towards the pumping chamber under magnetic field. The magnetic field and thus the amount of contraction is controlled by an electromagnet placed underneath the pump. The contraction of the top wall increases the pressure by constricting the fluid inside the flow chamber, forcing the fluid through the one-way valve in the front end. Simultaneously, the other valve in the rear experiences backpressure, which forces the geometry to seal itself, preventing the fluid from leaking backward. This one-way flow creates an effective pumping mechanism as it continually sends the fluid forwards. Simulation Methodology. Model Creation

[0124] The example proposed flap valve design and the proposed duckbill valve design both involve coupled magneto-solid-fluid interaction physics. Thus, the performance of the pump could best be predicted with the help of computer simulations rather than simplified 1D analytical models. In this study, simulations were carried out using COMSOL Multiphysics software. FIGS.1C and 2C show a schematic of the model created in COMSOL corresponding to the selected valve. To demonstrate the effectiveness of the flap valve, simulations were conducted with and without valves. FIG.1C shows the computational model with flap valves while FIG.2C shows the computational model with duckbill valves.

[0125] The geometric and material properties of the 2D model are given in Table 1a and 1b, while the dimensions are shown in FIGS.1D and 2D, corresponding to the selected valve, for convenience. The magnet is placed 0.35 mm below of the pump chamber. The length, height, and wall thickness of the pump chamber are 3.102 mm, 1.1 mm, and 0.1 mm, respectively. The elastic modulus of the pump material and average magnetic flux density acting on the upper wall are 1.2 MPa and 0.027 T, respectively.Attorney Docket Number: 10485-013WO1 Table 1a. Properties of the flap valve model Parameter Symbol Value Height of the pump chamber H 0.9 (mm)Parameter Symbol Value Height of the pump chamber H 0.900 (mm) [0012, t has constant structural and magnetic properties. The wall at the bottom does not deform in the presence of a magnetic field. It was assumed to be resting on a flat rigid surface so the deformation on the top wall can activate the fluid flow. The magnetic field analysis was conducted in AC / DC module, whereas the structural deformation of the pump chamber, including the top wall and one-way valves, and fluid flow through the pump chamber and valves were carried out in Solid Mechanics and Laminar Flow modules, respectively. An air domain exists outside of the structure of the pump chamber, and a laminar flow fluid domain exists inside the structure of the pump chamber. Simulation Procedure

[0127] The simulation procedure is illustrated with the flowchart shown in FIG.5. First, the variables, such as geometric and material properties, were defined. Since the simulation involves the deformation of the pump chamber and one-way valves, the moving mesh schemes were defined next. Then simulation geometry was created, which was followed by the material assignment to all solid and fluid domains. Next the respective boundaryAttorney Docket Number: 10485-013WO1 conditions were assigned in each physics module, i.e., AC / DC module, solid mechanics module, and laminar flow module. Then these different modules were communicated with each other to transfer data between different flow physics. For example, the upper wall of the pump chamber deforms under the influence of a magnetic field since it is a ferromagnetic material. To model this phenomenon, the AC / DC module was run to calculate the magnetic field over the entire domain, including all solid and fluid domains. Then this information was passed to the solid mechanics module to calculate the resultant deformation under the influence of the magnetic field. Similarly, the deformation data on the upper wall was transferred to the fluid domain via fluid-structure coupling between the solid mechanics and laminar flow modules. This reflected itself as a pressure load on the fluid domain at the fluid-solid interface, causing the fluid flow and thus, the pumping effect. While the fluid was pushed through the front valve, the pressure data on the valves were communicated, again, with the fluid-structure coupling. Note that the fluid-structure coupling was a two-way coupling, which provided convenience when the data was communicated back and forth between the solid and fluid domains. This was done by defining fluid-structure interaction multiphysics at all interfaces between the fluid and solid domains. Boundary conditions

[0128] As for the boundary conditions, a current excitation was added to the coil in the AC / DC module, and the force calculation interface was selected for the top edge of the upper wall of the pump chamber. This was to ensure that the Maxwell forces were transferred to the top edge for the desired deformation and thus, the resulting pumping effect. A sinusoidal time function and an external current density with a specific amplitude were applied to the core of the electromagnet. In the solid mechanics module, fixed support was added at the bottom wall of the pump chamber, and the Maxwell surface stress tensor (magnetic interaction force between the pump chamber and magnetic field) was selected in the boundary load interface. In the laminar flow module, the pressures at the left and right outlets were set to 0 Pa (gage). This was to allow the fluid freely to pass in and out from two terminals. In addition, a no-slip condition was applied to the walls surrounding the flow chamber. Computing Equations

[0129] Next, the governing equations for each physics involved will be discussed. The following equations were solved for the magnetic domain: ∇ ∙ ^ = 0 (1) ∇ × ^ = ^ (2)Attorney Docket Number: 10485-013WO1 ^ = ^^^^^ (3) ^ = ∇ × ^^^^^^^^^ (4) where ∇ is the gradient operator, ^ are the per^ meability of the magnetic flux density ^ is determined in Eq (1), which is calculated from Ampere’s law. By combining Eqs. (1), (2), and (3), the relation between ^and ^ is obtained which is shown in Eq. (4). Moreover, Eq. (5) shows the final equation of ^: ^ = ^^ + ^v × ^ + ^^(5) where ^ is the electrical conductivity, ^ is the electric field, ^^is the external current density, and v is the velocity of the conductor. The magnetic flux density ^ and external current density ^^can be calculated from Eqs. (6) and (7), respectively. ^ = ∇ × ^ (6) ^∙^ ^^= ^∙^ (7)

[0130] In Eqs. (6) and (7),of the coil of the electromagnet, ^ is the input electrical current to the coil, and a and b are the cross-sectional dimensions of the core. The magnetic field density ^ can be calculated from Eq. (8), when the external current density ^^is known ^^= ∇ × ^^^^^^^^^ − ^^ − ^v × ^ (8) The Maxwell stress is shown in Eq. (9), and in Eq. (10) the total stress, which is the result of magnetic stress and fluid pressure, is shown. ^. ^^^ !^""= −0.5^^^ ∙ ^^ + ^^ ∙ ^^^$(9) ^%&%^"= ^^^ !^""+ ^'(10) where ^ is the normal vector,is the stress due to fluid pressure.

[0131] In the fluid domain, the flow is set to laminar incompressible flow appropriately. The following equations were solved in the fluid domain: Steady continuity: (∇ ∙ )*"+,-= 0 (11) Navier-Stokes equations for stationary approach: (.)*"+,-∙ ∇ / )*"+,-= ∇ ∙ 0−1^ + 23 + 4 (12)Attorney Docket Number: 10485-013WO1 Navier-Stokes equation for the time-dependent approach: (5+6789:5% + (.)*"+,-∙ ∇ / )*"+,-= ∇ ∙ 0−1^ + 23 + 4 (13) where )*"+,-is energy, and 4 isEq. (14). 2 = ^^∇)*"+,-+ ^∇)*"+,-^$^ (14) And for the solidwere For stationary approach: 0 = ∇ ∙ ^FS^$+ 4v, 4 = > + ∇)?&",-(15) For the time-dependent approach: @ (5 +AB79:5%@= ∇ ∙ ^4C^$+ 4v, 4 = > + ∇)?&",-(16) In Eqs. (15) andtensor, and FS (F is the deformation gradient) is the first Piola-Kirchhoff stress tensor. Validity Study

[0132] When performing FEA / CFD simulations, it is a standard practice to conduct the mesh independency analysis. To do that, an initial simulation was run starting with course mesh and reducing the size of the mesh elements gradually. While doing so, the net pumped volume, which was the target design parameter, was recorded. The mesh size was reduced, in other words, the number of mesh elements were increased, until there is no significant change between the two successive cases. It was shown that the change in the net pumped volume was only 0.02% between grid numbers 4 and 5. Thus, grid number 4 is selected for the rest of simulations.

[0133] Although COMSOL Multiphysics is a proven simulation tool and has been employed by thousands of scientific studies in the literature, it is always wise and scientifically required to validate the simulation approaches with the existing studies in literature when experimental data is not readily available. To this end, the model presented in (Cao et al., 2020) was selected. All parameters, boundary conditions, magnetic flux density, and geometric dimensions were set to be the same. FIGS.6A-6C show the model with the main components as well as the dimensions.

[0134] The simulations were carried out by following the procedure outlined in FIG.5. The comparisons between the benchmark study and this study are provided in FIG.7. From FIG.7, it is seen that the upper wall displacement for both cases is the same for 75 mT, 145Attorney Docket Number: 10485-013WO1 mT, and 175 mT magnetic flux densities. In addition to the deformations, volume flow rates were also compared.

[0135] FIG.8 presents a comparison graph between the two cases. As seen from the figure, the volume flow rates closely matched between the two cases. The average percent error between the two cases is about 1.6%, with minimum and maximum deviations being 0.00% and 4.16% at 150 mT and 175 mT, respectively. This validates the simulation methodology, allowing us to continue with the full simulations of the proposed pump design. Results and Discussions

[0136] Simulations were carried out for one complete cycle, i.e., one contraction and one retraction phase. As an input magnetic field, 0.027 T was used, which was a reasonable value for the proposed pump size according to the literature. When actuated, the electromagnet attracts the magnetic particles inside the MRE, creating a downward pulling force. FIG.9A demonstrates the magnetic flux density acting on the upper wall across the length of the microchannel. It can be seen that the magnetic flux density is maximum at the two terminals of the microchannel and minimum in the middle. This makes sense because magnetic field concentrates on the upper MRE wall before returning to the electromagnet to complete the magnetic circuit.

[0137] The deformation of the upper MRE wall, under the influence of magnetic field, is shown in FIG.9B. The MRE wall bends downward due to the applied magnetic force, which agrees with expectations since the electromagnet is positioned underneath the bottom wall. The maximum deflection of the upper wall was calculated to 0.11 mm, which occurred in about the middle of the pump chamber.

[0138] FIG. 10A represents the velocity field inside the pump at t = 0.1 s when the maximum velocity occurs, while FIG. 10B shows the variation of total volume flow rate with time. The total volume flow rate is the summation of the outflow from both the left and right outlets. It should be noted that there is no inlet to the pump chamber.

[0139] FIG.11A shows the results for the same simulation configurations as in FIG.10A except that this time, one-way flap valves were added inside the pump chamber. A quantitative comparison between FIG.10B and 11B reveals that the inclusion of the flap valves reduced the backflow by about 10 times.

[0140] FIGS.12A and 12B display the results for the same simulation configurations as FIGS. 10A and 10B. However, in FIGS 12A and 12B, one-way duckbill valves were added inside the pump chamber. Quantitative comparison between FIGS.10B and 12B reveals that the inclusion of the duckbill valves reduced the backflow by about 7.5 times.Attorney Docket Number: 10485-013WO1

[0141] FIGS.13 and 14 show the volume flow rate during both contraction and retraction phases for (a) without valves and (b) with the flap valves. It is seen from the figure that with the addition of flap valves the net backward flow reduced significantly during the retraction phase.

[0142] The displacement and velocity field history of the micropump is shown in FIGS. 15A-14F for the contraction phase, i.e., t = 0 – 0.5 s. One can see that the right flap deforms toward the right, and the valve opens larger gradually, while the left flap pushes against the support and blocks the back flow. FIG. 15A shows the flow field at the beginning of the simulation at t = 0 s. In FIG.15B, the MRE is deformed downward, pushing the fluid toward the right terminal. In FIG.15C, the upper wall deforms further, and thus, the right flap bends more under increased fluid displacement (t = 0.2 s). In FIG.15D, the right flap deflects further toward the right, and left valve bends toward the left to prevent the backward flow (t = 0.3 sec). In FIG. 15E, deformation of upper wall and flaps continue (t = 0.4 s). In FIG.15F the deflections on the upper wall and flaps reach their maximum, and the maximum pumping effect is achieved (t = 0.5 s). At this time, the micropump is about to start the expansion phase.

[0143] FIG.16 shows the time history of net volume transferred through the right terminal of the micropump. The net volume transferred increased until the end of the contraction phase at t = 0.5 s. After this, the channel retracts, and the net pumped volume decreases.

[0144] The displacement and velocity field history of the micropump is shown in FIG. 17A-F for the contraction phase, i.e., t = 0 – 0.5 s. One can see that the right duckbill deforms and propel the fluid, while the left duckbill valve closes and blocks the backflow. FIG. 17A shows the flow field at the beginning of the simulation at t = 0 s. In FIG.17B, the MRE is started deforming downward, pushing the fluid toward the right terminal. Due to a large amount of fluid being enclosed in between the two valves, the fluid shows maximum velocity at the right valve in this stage. In FIG.17C, the upper wall deforms further, and thus, the right duckbill bends, but this time the tips of the right valve come closer to each other, thus decreasing fluid displacement (t = 0.2 s). In FIG.17D, the right duckbill valve deflects further and reduces the fluid flow, and the left valve closes completely to prevent the backward flow (t = 0.3 sec). In FIG.17E, deformation of the upper wall and duckbill valves continue (t = 0.4 s). In FIG.17F, the deflections on the upper wall (t = 0.5 s). At this time, the micropump is about to start the expansion phase.

[0145] The time history of net volume transferred through the right terminal of the micropump is displayed in FIG.18. During the contraction phase, the net volume transferredAttorney Docket Number: 10485-013WO1 constantly increased until the contraction phase ends at t = 0.5 s. Following this, the channel begins retracting, and the net pumped volume decreases. Parametric study

[0146] The effects of input parameters on the design target were also studied. Recalling that one goal was to increase the pumping effect of the proposed design, a parametric analysis was carried out to see the effects of various geometric and material properties, including the diameter of the pump chamber, the thickness of the upper MRE wall, the elastic modulus of the pump structure, and other geometric dimensions of the pump, on the net pumped volume. These input parameters for the flap valve implementation are listed in Table 2a with their respective ranges. The input parameters for the duckbill implementation can be found in Table 2b with their respective ranges. Table 2a. Geometric and material parameters for the parametric study Parameters Design values Values for parametric study Height of the pump chamber 0.9 mm 0.901, 0.902, 0.903, 0.904 mm Thickness of the upper wall 0.1 mm 0.11, 0.12, 0.13, 0.14 mm Elastic modulus 1.2 MPa 1.2, 5, 10, 15, 20, 25, 30, 35 MPa Valve spacing distance 3.102 mm 3.107, 3.112, 3.117, 3.122 mm Poisson’s ratio of the valve 0.45 0.25, 0.30, 0.35, 0.40, 0.45 Valve length 0.75 mm 0.75, 0.755, 0.76, 0.765 mm Valve width 0.06 mm 0.065, 0.07, 0.075, 0.08 mm Table 2b. Percent error of the flow rates between this study and benchmark study

[0054] . Parameters Design values Values for parametric study Height of the pump chamber 0.900 mm 0.900, 0.905, 0.910, 0.915, 0.920 mm Thickness of the upper wall 0.100 mm 0.100, 0.110, 0.120, 0.130, 0.140 mm Elastic modulus 1.200 MPa 1.200, 5.000, 10.000, 15.000, 20.000, 25.000, 30.000, 35.000 MPa Valve spacing distance 3.204 mm 3.204, 3.214, 3.224, 3.234, 3.244 mm Poisson’s ratio of the valve 0.450 0.250, 0.300, 0.350, 0.400, 0.450 Length of the Valve tip 0.560 mm 0.560, 0.570, 0.580, 0.590, 0.600 mm Poisson’s ratio of the upper 0.450 0.250, 0.300, 0.350, 0.400, 0.450 wall Parametric Simulation Results and Discussions

[0147] Figures 19A-25B show the effects of the diameter of the pump chamber, thickness of the upper wall, elastic modulus of the pump structure, valve spacing distance,Attorney Docket Number: 10485-013WO1 Poisson’s ratio, valve height, and valve width, on the net pumped volume. The parametric sweep studies were carried out in a way that the parameters that were not changed were set to their design values. These design values are listed in Table 5a and 5b.

[0148] Figure 19A shows that the net pumped volume is increasing with the height of the pump chamber. This is not only because the pump chamber is increased but also the modified aspect ratio of the flow chamber allows larger deformation of the upper wall, which would agree with the expectations.

[0149] The net pumped volume increases with the height of the pump chamber which is exhibited in Figure 19B. This increase is not only due to the pump chamber increase but also in part due to the modified aspect ratio of the flow chamber allowing larger deformation of the upper wall, which might be expected.

[0150] Figure 20A shows the variation of the net pump volume with respect to the thickness of the upper wall. As seen from the figure, the net pumped volume is decreasing with increasing values of the wall thickness, which makes sense since it becomes harder for the top wall to bend downward to create the pumping effect.

[0151] In Figure 20B the variation of the net pump volume with respect to the thickness of the upper wall is shown. As displayed in the figure, the net pumped volume is decreasing with increasing values of the wall thickness. This makes sense as it becomes harder for the top wall to bend downward to create the pumping effect with larger wall thicknesses.

[0152] The effect of the elastic modulus of the pump material on the net pumped volume is given in Figure 21A. As shown in the figure, as the elastic modulus is increasing the net pumped volume is decreasing, which would agree with expectations since the larger the elastic modulus becomes the stiffer the wall will be, resisting the deformation more strongly.

[0153] The effect of elastic modulus of the pump material on the net pumped volume is given in Figure 21B. As seen in the figure, the net pumped volume decreases with increasing elastic modulus. This would agree with expectations since the larger the elastic modulus becomes the stiffer the wall will be, resisting the deformation more strongly.

[0154] Figure 22A shows the influence of valve spacing distance on the net pumped volume. As shown in the figure, as valve spacing increases, the net pumped volume of the fluid also increases. This is because as the valve spacing becomes wider so does the pump chamber, increasing the amount of fluid pumped. It should also be noted that the length of the upper wall is proportional to the valve spacing distance. Thus, the axial length of the upper wall increasesAttorney Docket Number: 10485-013WO1 as the valve spacing becomes larger, and according to the fundamentals of the strength of materials, this will lead to larger deformations on the upper wall, enhancing the pumping effect.

[0155] The influence of valve spacing distance on the net pumped volume is shown in Figure 22B. As seen in the figure, the net pumped volume of the fluid also increases with increasing valve spacing. This is because as the valve spacing becomes wider, more amount of fluid can be housed in between the two valves, resulting in more fluid volume to be pumped, and thus enhancing the pumping effect.

[0156] The effect of the Poisson’s ratio of the valves is represented in Figure 23A. According to Hooke’s law, increased values of the Poisson’s ratio will result in decreased deformation of the upper wall, resulting in lower pumping effect, which agrees with expectations.

[0157] Figure 23B represents the effect of Poisson’s ratio on the valves. This also agrees with expectations since according to Hooke’s law, increased values of the Poisson’s ratio will result in decreased deformation of the valves, resulting in a lower pumping effect.

[0158] The effect of valve height on the net pumped volume is shown in Figure 24A. As seen, the net pumped volume decreases with increasing values of valve height. This is because as the height of the valve increases, it creates more resistance to flow and thus, reducing the pumping effect.

[0159] The influence of the upper wall’s Poisson’s ratio on the net pumped volume can be seen in Figure 24B, which yields the similar results as shown in Figure 23B. For this case, the increase in the Poisson’s ratio results in a decrease in the deformation experienced by the upper wall, deteriorating the pumping effect.

[0160] The effect of valve width on the net pumped volume is shown in Figure 25A. As the width of the valve is increasing, the net pumped volume is decreasing, which makes sense since the modified aspect ratio of the valves will make the valves stiffer, deteriorating the pumping effect.

[0161] The effect of the valve length on the pumping performance in terms of the net pumped volume is shown in Figure 25B. As seen, the net pumped volume continually decreases as the length of the valve increases. This is because the longer the valve is the higher the frictional losses are, reducing the pumping effect.

[0162] At least for the duckbill implementation, a parametric study revealed that each parameter contributed to the overall performance of the pump. Thus, an optimization study can determine the optimal values of these parameters for the maximum net pumped volume. To thisAttorney Docket Number: 10485-013WO1 end, an optimization study was performed letting the material properties remain constant and changing only the geometric parameters. Table 3 shows the optimum values for one example implementation of the valve spacing distance and height of the pump chamber, which were the only two parameters that were changed from the original design values. The optimal design for one example implementation was then compared with the original design, results of which are shown in Table 4. The comparisons revealed that the optimal design was capable of transferring 16.67% more fluid than the original model within one full cycle. Table 3. Optimal model parameters. Parameters Original model values (mm) Optimal model values (mm) Valve spacing distance 3.204 3.244 Height of the pump chamber 0.90 0.92 Table 4. Performance comparison between basic model and optimal model. Parameters Original Optimal design Net pumped volume of fluid design increased (%) Net pumped volume 2.10 2.45 16.67 (µL)

[0163] In this work, a comprehensive design methodology is presented for a novel magnetorheological (MR) micropump. To this end, a physics-based simulation methodology was adopted. The simulation approach was confirmed through a validity check study by replicating an existing study in the literature. The performance characteristics of the pump were presented and discussed. In addition, a parametric study was conducted to see the effects of important design parameters on the net pumped volume. The results of this study were also presented and discussed.

[0164] The findings of this study can be listed as follows: A micropump design was successfully demonstrated. A parametric study revealed that the net pumped volume: (a) increased by 4.43% as the diameter of the pump chamber increased from 0.901 mm to 0.904 mm for the flap valve implementation, and increased by 0.66% as the height of the pump chamber increased from 0.90 mm to 0.92 mm for the duckbill implementation; (b) decreased by 9.14% as the thickness of the upper wall increased from 0.11 mm to 0.14 mm for the flap valve implementation, and decreased by 2.83% as the thickness of the upper wall increased from 0.10Attorney Docket Number: 10485-013WO1 mm to 0.14 mm for the duckbill implementation; (c) decreased by 77.9% as the elastic modulus of the pump structure increased from 1.2 MPa to 35 MPa for the flap valve implementation, and decreased by 6.66% as the elastic modulus of the pump structure increased from 1.2 MPa to 35 MPa; (d) increased by 0.532% as the valve spacing distance increased from 3.107 mm to 3.122 mm for the duckbill implementation; (e) decreased by 6.34% as the Poisson ratio of valve increased from 0.25 to 0.45 for the flap valve implementation, and decreased by 1.21% as the Poisson ratio of valve increased from 0.25 to 0.45 for the duckbill implementation; (f) decreased by 7.43% as the valve length increased from 0.75 mm to 0.765 mm for the flap valve implementation, and decreased by 0.33% as the valve length increased from 0.56 mm to 0.60 mm for the duckbill implementation; (g) decreased by 31.57% as the valve width increased from 0.065 mm to 0.08 mm for the flap valve implementation; (h) decreased by 0.7% as the Poisson ratio of upper increased from 0.25 to 0.45 for the duckbill implementation; and (i) increased by 0.19% as the valve spacing distance increased from 3.204 mm to 3.244 mm for the duckbill implementation.

[0165] As a result of an optimization study, an example design is proposed, which can transfer 16.67% more fluid than the original model. The proposed micropump technology could be potentially utilized in various engineering applications, including drug delivery systems, artificial hearts, in-situ cell sorting and cytometry in laboratory environments, and thermal management techniques on PCBs. EXAMPLE #2 – A Comparative Evaluation of Magnetorheological Micropump Designs

[0166] A study was conducted to assess the performance characteristics of example magnetorheological micropump designs against other, existing micropump designs. Comparisons were performed based on physics-based simulations, and the fully coupled magneto-solid-fluid interaction (MFSI) simulations were carried out in COMSOL Multiphysics software. For a fair and meaningful comparison, both the material and geometric properties were kept the same, and the simulations were run for one complete pumping cycle. Highly coupled MFSI simulations were carried out in COMSOL Multiphysics software (v5.6).

[0167] The results showed that the proposed flap and duckbill valve models could pump 1.09 µL and 1.16 µL respectively in 1 sec, more than any existing pump devices. Moreover, at 0.5 sec, when the magnetic flux density was maximum, the flap and duckbill valve models could pump almost twice as fluid as some of the existing valve models did. The results also demonstrated that the flap and duckbill valve models were nearly five times faster than some of existing models. In conclusion, the proposed two micropump models could propel more net fluidAttorney Docket Number: 10485-013WO1 volume than the existing micropump designs, experienced low leakage during the contraction and expansion phase, and had faster response times. The present study provides valuable insights for micropump designs, which have an extensive range of application areas, ranging from insulin dosing systems for T1D patients to artificial organs to transport blood and from organ-on-chip applications to micro-cooling systems. EXAMPLE #3 – A Proof-of-Concept Study of a Magnetorheological Micropump

[0168] A study was conducted on a flap valve micro-fluidic pump that relies on an electromagnetic actuation mechanism. A Finite Element Analysis (FEA) / Computational Fluid Dynamics (CFD)-based approach was embraced for the design of the device due to the coupled electromagnetic-fluid-structural interactions in the device. Simulations were carried out in COMSOL Multiphysics software. The performance characteristics of the pump were presented and discussed, and a parametric study was conducted to see the effects of important design parameters on the net pumped volume, similar to Example #1. After the simulation studies, a working prototype pump with a 10.22x7.67x51.11 mm (WxHxL) was 3D printed. The experimental plan for the working prototype was discussed for further studies. The presented study lays the foundation for future studies where the pump size may be reduced to under 1 mm. The proposed micropump could potentially be used in a broad range of applications, such as an insulin dosing system for Type 1 Diabetic patients, artificial organs to transport blood, organ- on-chip applications, and so on.

[0169] The presently described study is the same or substantially similar to the above- described studies (with respect to, at least, the proposed designs, the simulation procedure, and the governing equations), so the description of this study will pick up with the Model Geometry.

[0170] Model Geometry – The 2D model of this study (e.g., a model as shown in FIGS. 1A and 1B) included material characteristics and dimensions as provided in Table 5. The electromagnetic device is 2.67mm below the pump chamber. The length, height, and wall thickness of the pumping chamber are 51.11mm, 7.67mm and 0.59mm. The elastic modulus of the elastomer is 10.2MPa. The average magnetic flux density acting on the upper wall is 0.042T. TABLE 5: PROPERTIES OF THE FLAP VALVE MODEL Parameter Symbol Value ) ) ) )Attorney Docket Number: 10485-013WO1 Distance between the pump D 2.67 (mm) chamber and electromagnet )

[0171] In tas presented for a novel magnetorheological (MR) micropump. To this end, a physics-based simulation methodology was adopted. The simulation approach was confirmed through a verification study by replicating an existing study in the literature. The performance characteristics of the pump were presented and discussed. In addition, a parametric study was conducted to see the effects of important design parameters on the net pumped volume. The results of this study were also presented and discussed.

[0172] In this study, the mechanical properties of the MRE and the pump structure were assumed to be equivalent to that of silicon. Although this assumption was confirmed by previous studies, a material characterization study needs to be performed to determine the true material properties of both the MRE and pump structure. The material properties are known to be dependent on the manufacturing processes. More specifically, in 3D printing technology, the mechanical properties of the printed material depend on the build orientation and can become non-uniform and thus, anisotropic. Not only that, during the printing process defects may occur, which can alter the mechanical properties of the printed parts even further. Therefore, material characterization studies was conducted on 3D printed MRE and pump structures as part of future studies.

[0173] The major findings of this study can be listed as follows: The parametric study revealed that the net pumped volume: (a) increased by 8.60% as the diameter of the pump chamber increased from 7.67 mm to 7.71 mm; (b) decreased by 30.57% as the thickness of the upper wall increased from 0.59 mm to 1.09 mm; (c) decreased by 2.95% as the elastic modulus of the pump structure increased from 10.2 MPa to 30 MPa; (d) increased by 8.57% as the valve spacing distance increased from 26.840 mm to 26.845 mm; (e) decreased by 9.21% as the Poisson ratio of valve increased from 0.25 to 0.45; (f) decreased by 21.41% as the valve length increased from 6.43 mm to 6.73 mm; and (g) decreased by 11.04% as the valve width increased from 0.805 mm to 0.825 mm.Attorney Docket Number: 10485-013WO1

[0174] As a result of an optimization study that was conducted, an optimum design is proposed, which can transfer 51.50% more fluid than the initial model. The proposed micropump technology could be potentially utilized in various engineering applications, including drug delivery systems, artificial hearts, in-situ cell sorting and cytometry in laboratory environments, and thermal management techniques on PCBs.

[0175] Experimental Design – The schematic diagram of the developed experimental setup is shown in FIG.26A, according to one implementation. The micropump is connected with the left and right graduated cylinders through pipes. There is one connector on each side of the pump to connect it with pipes. An electromagnet is placed at the bottom of the pump and is used to generate the magnetic field to improve the actuation efficiency and controllability of the pump. A stand and clamping mechanism are used to hold the left and right graduated cylinders. To visualize the pumping process, water mixed with black dye is used in the pulse pump system. The flow rate could be calculated by the volume change of liquid and the pumping time. The flow is supposed to flow from the left graduated cylinder to the right graduated cylinder due to the pumping of the micropump.

[0176] A picture of the 3D printed micropump prototype is given in FIG. 26B. The length, height, and width of the prototype is 51.11 mm, 7.67 mm, and 10.22 mm, respectively. A high-resolution UV-LCD resin 3D printing technology was used to fabricate prototype. Carbonyl Iron particle will be loaded with resin in the next stage. For this purpose, a fundamental study on the printability of the mixture of carbonyl Iron Particle suspended in the UV-resin will be carried out. The ratio of the Carbonyl Iron particle and resin will affect the viscosity of the resultant resin. For this purpose, different ratios with different viscosities will be tested on a UV- LCD 3D printer to study the printability of the resin mixtures in future. Therefore, a complete parameter study for the printability of the resin-particle mixture will be carried out, and the optimum mixing ratio as well as printing parameters will be obtained through a series of experiments. Also, other 3D printing technologies such as 3D Inkjet printing will be tried as an alternative.

[0177] After successful fabrication of the MRE micropump, experiments may be conducted to determine the net pumped volume under the magnetic field 0.042 T. This experimented net pumped volume will then be compared with the simulated results. A picture of the experimental setup is shown in FIG.26C. Example #4 – A MAGNETORHEOLOGICAL PERISTALTIC MICROPUMP FOR INSULIN DELIVERYAttorney Docket Number: 10485-013WO1

[0178] In this study, a physics-based 3D simulation study was carried out in COMSOL Multiphysics software, integrating the Magneto-Solid-Fluid Interaction model to evaluate the performance of the proposed pump design (e.g., the device of FIG.1A and / or FIG.5A). The computational findings indicate that the pump can transfer up to 1.99 μL of fluid in a single pumping cycle, achieving this flow rate within 0.41 seconds with a magnetic field strength of 150 mT. Apart from insulin delivery for T1D patients, the versatility of this micropump extends to a wide range of applications, including transporting blood in artificial organs, facilitating organs, facilitating organ-on-chip experiments, and enhancing micro-cooling devices.

[0179] In this study a complete cycle of the simulation was conducted for 1 second, including the contraction and retraction stages. The simulation utilized a magnetic flux density of 150 mT. The following discussion explores the specific outcomes derived from this simulation, providing insight into the interaction between magnetic forces, wall deformation, and characteristics of the fluid flow. Generated Magnetic Flux Density and Total Magnetic Energy

[0180] The condition of the magnetic flux density with respect to changes of time has been discussed in this section. The phenomenon shown in FIG.27 demonstrates the maximum magnetic flux that occurs at 0.5 second, while FIG.28A shows the equivalent variation in magnetic flux over time. There is a consistent increase in the magnetic flux, contributing to the attractive force acting on magnetic particles within the magnetorheological elastomer (MRE), resulting in a downward pulling force. The magnetic flux density is highest at the two terminals of the magnets. At the same time, it is lowest at midpoint. In figure it is also visible that the most increased magnetic flux, 144.21 mT, shows at the corner of the permanent magnet. This behavior is rationalized by the concentration of the magnetic field on the upper MRE wall before completing the magnetic circuit by returning to the magnet.

[0181] Notably, FIG.28B shows that deformation only needs 6.16 µJ of total magnetic energy, which is a low value compared to other studies reported in the literature. The low total magnetic energy demand suggests a considerable reduction in power consumption, making the proposed system energy efficient. Generated Stress and the Deformation of the Upper Wall

[0182] As the magnetic flux density rises, a noticeable effect is seen on the upper wall of the channel, as seen in the following figures. FIG.29 depicts the stress applied to the upper wall because of the magnetic field, whereas FIG.31 exhibits the subsequent deformation. TheAttorney Docket Number: 10485-013WO1 stress on the upper wall is a result of the magnetic forces acting on the material, leading to deformation. The measurements were considered at the midpoint of the upper wall. Both images demonstrate that the maximum deformation occurs in the channel's middle section, which is consistent with our assumptions due to the magnet's positioning beneath the lower wall. Notably, in both FIG.30 and FIG.32, the stress and deformation peak at 0.5 seconds, which is consistent with the maximum magnetic flux at that time. The maximum stress exerted on the upper wall due to the magnetic flux is 1673.90 N / m², resulting in a deformation of the wall reaching up to 0.2 mm. Furthermore, the figures illustrate that the upper wall is not restored to its initial position after one second. This phenomenon results from the material's silicon content, which leads to its enduring irreversible deformation for a limited period. If the material is left in its distorted state for a while, it will eventually return to its original phase. Net Pumped Volume and Velocity Field

[0183] Due to the downward deformation of the upper wall induced by the magnetic field, a resultant force propels the fluid within the channel, facilitating the transfer of fluid from the channel to the outlet. At the maximum deformation during the contraction stage, the velocity profiles have been presented in FIG.33, while FIG.34 and FIG.35 show the changes in mass flow rate and net pump volume over the entire cycle. The total volume flow rate is the sum of the outflow from the left and right ends, and it was calculated at the channel's outlet based on the mass flow rate. The data clearly shows that the mass flow rate and the volume flow rate peak at the same time, 2.59 mg / s and 1.99 µL / s, respectively. Backflow is indicated by negative values during the expansion stage, with a backflow rate of 0.22 µL / s. Interestingly, this backflow is quite small compared to the net exit volumetric flow. This phenomenon can be explained by the way the left valve functions, which is like a one-way valve in that it permits forward flow during the expansion stage but prevents reverse flow. This action helps the fluid go through the channel in an effective and unidirectional manner.

[0184] In summary, this study introduces a comprehensive design methodology for a novel magnetorheological (MR) micropump, employing a physics-based simulation approach. The validity of the simulation methodology was established through a replication study of an existing work in the literature. The performance characteristics of the micropump were thoroughly presented and discussed, leading to the following key findings: Successful demonstration of a novel micropump design. The 0.2 mm deformation of the MRE upper wall required 6.16 µJ of magnetic energy under an applied field of 150 mT. The maximum flow rate under magnetic actuation was calculated to be 1.99 µL / s (or 2.59 mg / s).Attorney Docket Number: 10485-013WO1 Configuration of Certain Implementations

[0185] The construction and arrangement of the systems and methods as shown in the various exemplary implementations are illustrative only. Although only a few implementations have been described in detail in this disclosure, many modifications are possible (e.g., variations in sizes, dimensions, structures, shapes and proportions of the various elements, values of parameters, mounting arrangements, use of materials, colors, orientations, etc.). For example, the position of elements may be reversed or otherwise varied, and the nature or number of discrete elements or positions may be altered or varied. Accordingly, all such modifications are intended to be included within the scope of the present disclosure. The order or sequence of any process or method steps may be varied or re-sequenced according to alternative implementations. Other substitutions, modifications, changes, and omissions may be made in the design, operating conditions, and arrangement of the exemplary implementations without departing from the scope of the present disclosure.

[0186] The present disclosure contemplates methods, systems, and program products on any machine-readable media for accomplishing various operations. The implementations of the present disclosure may be implemented using existing computer processors, or by a special purpose computer processor for an appropriate system, incorporated for this or another purpose, or by a hardwired system. Implementations within the scope of the present disclosure include program products including machine-readable media for carrying or having machine- executable instructions or data structures stored thereon. Such machine-readable media can be any available media that can be accessed by a general purpose or special purpose computer or other machine with a processor. By way of example, such machine-readable media can comprise RAM, ROM, EPROM, EEPROM, CD-ROM or other optical disk storage, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to carry or store desired program code in the form of machine-executable instructions or data structures, and which can be accessed by a general purpose or special purpose computer or other machine with a processor.

[0187] When information is transferred or provided over a network or another communications connection (either hardwired, wireless, or a combination of hardwired or wireless) to a machine, the machine properly views the connection as a machine-readable medium. Thus, any such connection is properly termed a machine-readable medium. Combinations of the above are also included within the scope of machine-readable media. Machine-executable instructions include, for example, instructions and data which cause aAttorney Docket Number: 10485-013WO1 general-purpose computer, special purpose computer, or special purpose processing machines to perform a certain function or group of functions.

[0188] Although the figures show a specific order of method steps, the order of the steps may differ from what is depicted. Also, two or more steps may be performed concurrently or with partial concurrence. Such variation will depend on the software and hardware systems chosen and on designer choice. All such variations are within the scope of the disclosure. Likewise, software implementations could be accomplished with standard programming techniques with rule-based logic and other logic to accomplish the various connection steps, processing steps, comparison steps and decision steps.

[0189] It is to be understood that the methods and systems are not limited to specific synthetic methods, specific components, or to particular compositions. It is also to be understood that the terminology used herein is for the purpose of describing particular implementations only and is not intended to be limiting.

[0190] As used in the specification and the appended claims, the singular forms “a,” “an” and “the” include plural referents unless the context clearly dictates otherwise. Ranges may be expressed herein as from “about” one particular value, and / or to “about” another particular value. When such a range is expressed, another embodiment includes from the one particular value and / or to the other particular value. Similarly, when values are expressed as approximations, by use of the antecedent “about,” it will be understood that the particular value forms another embodiment. It will be further understood that the endpoints of each of the ranges are significant both in relation to the other endpoint, and independently of the other endpoint.

[0191] “Optional” or “optionally” means that the subsequently described event or circumstance may or may not occur, and that the description includes instances where said event or circumstance occurs and instances where it does not.

[0192] Throughout the description and claims of this specification, the word “comprise” and variations of the word, such as “comprising” and “comprises,” means “including but not limited to,” and is not intended to exclude, for example, other additives, components, integers or steps. “Exemplary” means “an example of” and is not intended to convey an indication of a preferred or ideal embodiment. “Such as” is not used in a restrictive sense, but for explanatory purposes.

[0193] Disclosed are components that can be used to perform the disclosed methods and systems. These and other components are disclosed herein, and it is understood that whenAttorney Docket Number: 10485-013WO1 combinations, subsets, interactions, groups, etc. of these components are disclosed that while specific reference of each various individual and collective combinations and permutation of these may not be explicitly disclosed, each is specifically contemplated and described herein, for all methods and systems. This applies to all aspects of this application including, but not limited to, steps in disclosed methods. Thus, if there are a variety of additional steps that can be performed it is understood that each of these additional steps can be performed with any specific embodiment or combination of implementations of the disclosed methods.

Claims

Attorney Docket Number: 10485-013WO1 CLAIMS 1. A fluid delivery device, comprising: a fluid chamber having a first end and a second end, the fluid chamber partially defined by a first one-way valve at the first end, a second one-way valve at the second end, a first wall comprising a magnetorheological elastomer, and a second wall opposite from the first wall; and an electromagnetic actuator disposed adjacent to the fluid chamber and configured to apply a magnetic field; wherein the fluid chamber is adjustable between a first configuration and a second configuration, wherein, upon application of the magnetic field, (i) the first wall deforms towards an interior of the fluid chamber, (ii) the first one-way valve closes, and (iii) the second one-way valve opens, thereby placing the fluid chamber in the second configuration and moving a fluid in a flow direction from the first end to the second end and out of the fluid chamber.

2. The fluid delivery device of claim 1, wherein each of the first one-way valve and the second one-way valve comprises: a flap valve protrusion extending a first distance from the first wall into the interior of the fluid chamber along a first axis, the first axis being substantially perpendicular to the first wall; and a base support extending a second distance from the second wall into the interior of the fluid chamber along a second axis, the second axis being substantially parallel to the first axis, the first axis being offset from the second axis along the flow direction closer to the second end; wherein, in the first configuration, the distance between the first wall and the second wall is less than the sum of the first distance and the second distance such that the flap protrusion and the base support overlap to define a gap.

3. The fluid delivery device of claim 2, wherein, in the second configuration, the flap valve protrusion of the first one-way valve moves towards the base support of the first one-way valve to close the gap of the first one-way valve; and the flap valve protrusion of the second one-way valve moves away from the base support of the second one-way valve to extend the gap of the second one-way valve.Attorney Docket Number: 10485-013WO1 4. The fluid delivery device of claim 1, where each of the first one-way valve and the second one-way valve are duckbill valves.

5. The fluid delivery device of claim 1, where each of the first one-way valve and the second one-way valve comprises: a first protrusion integrally coupled to the first wall, the first protrusion comprising: a first connector portion coupled to and extending out from the first wall; a first contoured portion coupled to the connector portion, the contoured portion extending (i) along the flow direction from the first end towards the second end of the fluid chamber and (ii) at least partially towards the second wall at an angle with respect to the flow direction; and a first valve tip coupled to the contoured portion, the valve tip extending along the flow direction; and a second protrusion coupled to the second wall immediately opposite the first protrusion; wherein the second protrusion is substantially similar to the first protrusion such that the first valve tip is disposed adjacent and parallel to a second valve tip of the second protrusion, the first valve tip and the second valve tip defining a gap.

6. The fluid delivery device of claim 5, wherein, in the second configuration, the first and second valve tips of the first one-way valve move towards each other to close the gap of first one-way valve; and the first and second valve tips of the second one-way valve move away from each other to extend the gap of the second one-way valve.

7. The fluid delivery device of claim 1, further comprising a third one-way valve, wherein the fluid chamber is a first fluid chamber, the second and third one-way valves defining a second fluid chamber disposed further along the flow direction with respect to the first fluid chamber; and a second electromagnetic actuator disposed adjacent to the second fluid chamber.Attorney Docket Number: 10485-013WO1 8. The fluid delivery device of claim 7, wherein the first electromagnetic actuator is configured to apply a first magnetic field to move the first fluid chamber from the first configuration to the second configuration; wherein, after the first magnetic field is applied, the first magnetic field is removed and the second electromagnetic actuator applies a second magnetic field to move the second fluid chamber from the first configuration to the second configuration, moving fluid from the first fluid chamber to the second fluid chamber.

9. The fluid delivery device of claim 1 further comprising a plurality of one-way valves defining a plurality of fluid chambers with a corresponding plurality of electromagnetic actuators, wherein a plurality of magnetic fields are applied and removed sequentially to (i) move each of the plurality of fluid chambers between a first and second configuration, and (ii) move fluid between the plurality of fluid chambers along the flow direction.

10. The fluid delivery device of claim 1, wherein the first and second one-way valves and the second wall comprise a base matrix (e.g., silicon), wherein magnetorheological elastomer of the first wall comprises a base matrix (e.g., silicon) and micro- or nano-sized ferromagnetic iron particles embedded within the base matrix.

11. The fluid delivery device of claim 10, where the first wall comprises polydimethylsiloxane (PDMS).

12. The fluid delivery device of claim 1, wherein the magnetorheological elastomer is isotropic or non-isotropic.

13. The fluid delivery device of claim 1, wherein the fluid is a medication.

14. The fluid delivery device of claim 1, further comprising at least one side wall extending between the first wall and the second wall, the at least one side wall further defining the fluid chamber.Attorney Docket Number: 10485-013WO1 15. A system comprising: a plurality of fluid delivery devices, each device comprising: a fluid chamber having a first end and a second end, the fluid chamber partially defined by a first one-way valve at the first end, a second one-way valve at the second end, a first wall comprising a magnetorheological elastomer, and a second wall opposite from the first wall, wherein the fluid chamber is movable between a first configuration and a second configuration; a plurality of electromagnetic actuators disposed adjacent to each of the fluid chambers of the plurality of fluid delivery devices, each electromagnetic actuator being configured to apply a magnetic field to deform the first wall towards the interior of the fluid chamber, close the first one-way valve, and open the second one-way valve, moving fluid in the flow direction; and a control system in electrical communication with each of the plurality of electromagnetic actuators, the control system configured to actuate the plurality of electromagnetic actuators in a pre-defined sequence to move fluid from one end of the plurality of fluid delivery devices to a second end of the plurality of fluid delivery devices.

16. A method of fabricating the fluid delivery device of claim 1.

17. A method of fabricating a fluid delivery device having a valve system and a magnetorheological elastomer, the method comprising: 3D printing the valve system using a base material; and 3D printing the magnetorheological elastomer on a first wall of the fluid delivery device, the magnetorheological elastomer being integrally formed with the base material of the valve system.

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