WO2021194359A1

WO2021194359A1 - Syringe pump

Info

Publication number: WO2021194359A1
Application number: PCT/NZ2021/050050
Authority: WO
Inventors: Robert Lauwrence Ward; Reuben Samuel Osborne; Martin Alexander Keith Williams
Original assignee: Robert Lauwrence Ward; Reuben Samuel Osborne; Martin Alexander Keith Williams
Priority date: 2020-03-27
Filing date: 2021-03-26
Publication date: 2021-09-30
Also published as: AU2021241336A1

Abstract

This disclosure may broadly be said to consist in a syringe pump to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body. A housing contains a motor and an electronic controller. A syringe mount mounts the body of the syringe on the housing to prevent relative movement between the syringe body and the housing. An actuator is movably mounted on the housing relative to the syringe mount, and engages the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body. The mount may comprise shielding to shield the syringe from the ambient environment. In other configurations the housing of the syringe mount enables multiple syringe pumps to be mounted/stacked together. In other configurations, all components of the pump are located within a notional envelope defined by the outer margins of the housing.

Description

A SYRINGE PUMP

Field of the Disclosure

This disclosure relates to a syringe pump and more particularly, the disclosure relates to a microfluidics syringe pump for controlling a flow of fluid to/from one or more microfluidic chip(s).

Background

Syringe pumps are often used to deliver a relatively precise flow rate and/or volume of a fluid. Such pumps are often used in a medical environment to deliver medicaments to a patient. Such pumps are also often used in a scientific/research environment, for example in chemical or biomedical laboratories. Such pumps can also be used in microfluidics to deliver fluid to a microfluidic chip.

Various syringe pumps are on the market. Such pumps typically hold one or more syringes of the type comprising a hollow syringe body, a movable plunger in the body, and a dispensing nozzle or needle. Such pumps include a motor which drives an actuator to move the syringe plunger to dispense the required flow rate and/or volume of a fluid in the syringe. Such syringe pumps are typically relatively large and unwieldy, are often connected to multiple cables, require an external power source, and are not always easy to control and/or able to meter the desired flow rate and/or volume as precisely as desired.

Object of the Disclosure

It is therefore an object of the disclosure to provide a syringe pump which overcomes or at least ameliorates one or more disadvantages of the prior art, or alternatively to at least provide the public with a useful choice.

Summary of Disclosure

Accordingly in one aspect the disclosure may broadly be said to consist in a syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein the syringe mount comprises shielding configured to shield at least part of the syringe from the ambient environment.

Accordingly in another aspect the disclosure may broadly be said to consist in a syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein the syringe pump comprises: a user interface, movably mounted on the housing, and configured to allow the user to interact with the user interface via relative movement between the user interface and the housing or relative movement between the user interface and the user, and configured to send a signal to the electronic controller indicative of both the position of the user interface, and the speed of movement of the user interface; the electronic controller generating a motor control signal in dependence upon both the position of the user interface, and the speed of movement of the user interface.

Accordingly in a further aspect the disclosure may broadly be said to consist in a syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein : the housing defining an envelope defined by the uppermost, lowermost and lateralmost parts of the housing, the actuator being contained within the envelope.

Accordingly in another aspect the disclosure may broadly be said to consist in a syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein : the housing is generally oblong being longer than it is wide and comprises a longitudinal axis along which the actuator moves; wherein the width of the housing is less than three times the diameter of the syringe body.

The syringe pump may comprise a user interface, movably mounted on the housing, and configured to allow the user to interact with the user interface via relative movement between the user interface and the housing or relative movement between the user interface and the user, and configured to send a signal to the electronic controller indicative of both the position of the user interface, and the speed of movement of the user interface; the electronic controller generating a motor control signal in dependence upon both the position of the user interface, and the speed of movement of the user interface.

The electronic controller may be configured to generate a user interface speed signal in dependence upon processing of both the speed of the user interface when moved by the user, and a predetermined and prestored relationship between the user interface speed signal and the speed of movement of the user interface, wherein the electronic controller is configured to select the user interface speed signal that corresponds to the measured speed of movement of the user interface in the predetermined and prestored relationship.

The electronic controller may be configured to generate the motor actuation signal in dependence upon a predetermined relationship between the motor speed and the position of the user interface, wherein the motor control signal is based on a function of the calculated user interface speed signal for different user interface positions.

The electronic controller may be configured to measure the relative speed of the user interface multiple times per second.

The electronic controller may be configured to delay any movement of the syringe actuator when the user interface is moved from one direction to another, that is when the user is intending to change the direction of fluid flow through the syringe.

The delay may be between 0.1 and 2 seconds, or between 0.25 and 1 second, or between 0.35 and 0.6 seconds.

The user interface may comprise the only actuator that is required to control the flow rate and/or volume of fluid dispensed. The user interface may be a rotary actuator, such as a continuously rotary actuator.

The user interface may be an electro mechanical actuator configured to convert mechanical movement of the user interface by the user into an electronic control signal.

The housing may be generally oblong being longer than it is wide and comprises a longitudinal axis along which the actuator moves. The housing may have a length, the length being in the range of 150-250mm, or 175 to 225mm, or 185 to 205mm. The housing may have a width, the width being in the range of 30 to 70mm, or 40 to 60mm, or 45 to 55mm. The width of the housing is less than three times the diameter of the syringe body. The housing may have a height, the height being in the range of 30 to 70mm, or 40 to 60mm, or 45 to 55mm. The height of the housing may be less than 10 times the diameter of the syringe body.

The housing may comprise a planar base and a planar top surface spaced from the planar base, the base and top surface being configured such that the syringe pump can be vertically stacked with another syringe pump.

The housing may comprise a pair of opposed planar sides that are configured to allow the syringe pump to be horizontally stacked with another syringe pump.

The housing may comprise a footprint of less than 15000 mm², or less than 12000 mm²', or less than 10000mm².

The housing may define an envelope defined by the uppermost, lowermost and lateral most parts of the housing, the actuator being contained within the envelope.

The housing may have a width, the actuator not laterally projecting beyond the width. The housing may have a height, the actuator not vertically projecting beyond the height.

The syringe mount may be elongate and engages/contains a portion of the length of the syringe body.

The syringe mount may engage/contain around half of the length of the syringe body.

The syringe mount may project from one end of the housing.

The syringe mount may comprise shielding configured to shield at least part of the syringe from the ambient environment.

The shielding may comprise thermal shielding configured to thermally insulate at least part of the syringe from the ambient environment.

The shielding may comprise air flow shielding configured to shield the at least part of the syringe from ambient air currents/flow.

The syringe mount may comprise an elongate shield body, and an elongate shield cover configured to be mounted on the elongate shield body and retain the syringe on the syringe mount.

The elongate shield body may comprise a channel into which the syringe body can be inserted to mount the syringe to the shield mount.

The elongate shield cover may comprise a channel into which the syringe body is received.

The shield mount may comprise a retainer configured to engage the syringe body and prevent longitudinal movement of the syringe body along the longitudinal axis of the shield mount. The retainer may comprise a radial outwardly directed recess into which part of the syringe body is received.

The housing may comprise an enclosure, spaced from the syringe mount, and containing the motor and the electronic controller and the user interface.

The enclosure may comprise any one or more of: a) At least one motor which is configured to drive shaft(s), either directly or via an intermediate gear assembly. b) At least one electronic controller, configured to output a motor control signal to control the speed and direction of rotation of the motor. c) A user interface configured to generate two signals that are input to the electronic controller i. a user interface signal indicative of the position of the user interface; and ii. a user interface speed signal indicative of the speed of movement of the user interface, when moved by the user. d) A single combined power and data connector, for example a USB port, configured to be connected to a combined power and data cable configured to supply the syringe pump with power and/or data as required, via a single cable. e) Optionally at least one battery and/or supercapacitor to power the motor and/or to power the electronic controller and/or to power the user interface. The battery and/or supercapacitor may be internal or external of the enclosure. In the example illustrated, a separate battery and/or supercapacitor may be provided which plugs into the enclosure via a power connector. f) Optionally one or more user displays, such as LEDs, which may be multicolour LEDs, and/or display panels, which may comprise one or more LCD or OLED panels. The display panel may be configured to be controlled to display parameters of the fluid being delivered, such as flow rate, or volume dispensed for example, or any other desired parameter. g) Optionally one or more user programmable buttons. h) Optionally one or more cooling devices, such as one or more cooling fans. i) Optionally an external I/O port for connecting the pump to pump accessories. j) Optionally a sound emitter such as a beeper or speaker to provide audible warnings/audible feedback or other audible information to the user.

The power and data connection may be the same connector, the syringe pump further comprising a single external cable, the single external cable being configured to supply both power and data to the syringe pump. The power and data connector may be a USB connector.

The enclosure may be spaced from the syringe mount along the longitudinal axis of the housing.

The enclosure and syringe mount may both project upwardly from a base of the housing.

The syringe pump may comprise less than 30 components, where the electronic controller is considered to be a single component, and preferably less than 20 components.

According to another aspect of this disclosure there is provided a fluid dispensing system comprising the syringe pump of any one of the above statements, at least one syringe, and dispensing tubing configured to be connected to the syringe.

The system may comprise a plurality of syringe pumps.

The system may comprise a plurality of syringes.

The system may comprise a microfluidic chip configured to receive fluid from the syringe.

According to another aspect of this disclosure there is provided an electronic controller configured to comprise part of the syringe pump of any one of the above statements. Further aspects of the disclosure, which should be considered in all its novel aspects, will become apparent from the following description.

Drawing Description A number of embodiments of the disclosure will now be described by way of example with reference to the drawings in which:

Figure 1 is a perspective view of a syringe pump in accordance with this disclosure, with the syringe mounted on a syringe mount of the syringe pump. Figure 2 is a plan view of a plurality of the syringe pumps of Figure 1 in use with a plurality of syringes and a microfluidic chip. The components shown in this figure (the syringe pumps and microfluidic chip) are shown approximately to scale to illustrate example proximity of the syringe pumps to each other, and to the microfluidic chip. Figures 3a and 3b are enlarged side and exploded perspective views of the syringe mount of the syringe pump of Figures 1 and 2.

Figures 4a to 4d are further views corresponding to Figure 3.

Figure 5a is an end view of one component of an alternative syringe block of the syringe pump of Figures 1 and 2, and Figure 5b is a perspective view of the syringe mount of the syringe pump of Figures 1 and 2.

Figures 6a and 6b are perspective views of the alternative syringe block and syringe mount of Figure 5, showing the block in a first, raised condition, with the syringe omitted.

Figure 7 is a perspective view of the alternative syringe block and syringe mount of Figure 5, showing the block in a lowered condition, with the syringe omitted.

Figure 8 and 9 are perspective views of the alternative syringe block and syringe mount of Figure 5, showing the block in a second, lowered condition, showing the syringe mounted on the syringe mount. Figure 10 is a graph showing a relationship between a calculated variable

(referred to here as the a-value), and the user interface speed (where the user interface is a knob having a rotation speed), in accordance with this disclosure.. Figure 11 is a graph showing a relationship between the desired flow rate of fluid from a syringe and the position of a user interface of the syringe pump, in accordance with this disclosure.

Figure 12 is a schematic control diagram showing control steps of a user interface, where the user interface comprises a rotary user interface such as a knob in this example, for different positions of the user interface.

Any dimensions shown in the Figures are exemplary only, included for illustrative purposes, and not limiting on the scope of this disclosure and/or claims.

Detailed Description of the Drawings Throughout the description like reference numerals will be used to refer to like features in different embodiments.

Referring first to Figure 1, a syringe pump 1 comprises an elongate, cuboidal housing 3 comprising a planar base 5. At one end of the base 5 is an upstanding syringe mount 7, and at the other end of the base 5, distal from the syringe mount 7, is a cuboidal electronics and motor enclosure 9. Extending between the syringe mount 7 and the enclosure 9 are a pair of parallel, horizontal guide rails 11 on which a carriage 13 is movably mounted, the rails 11 extending through respective elongate bores in the carriage 13. A lead screw 12 extends from the motor housed in enclosure 9 to a bearing (not shown) mounted in the end wall 7A of syringe mount 7. Rotation of the lead screw 12 engages the threads of the lead screw 12 with the bore in the carriage 13 to drive the carriage 13 along the rails 11, towards or away from the syringe mount 7. The rails 11 provide stability to, and guide, the carriage 13, and resist rotation, lateral, and vertical movement of the carriage 13 relative to the housing 3.

The syringe mount 7 comprises the upstanding end wall 7A of the housing 3, and an elongate syringe block 7B which is mounted on and projects outwardly from end wall 7A so as to project from the end of the housing 1 in a direction substantially parallel with the direction of movement of the carriage 13 along shafts 11. As can best be seen in Figure 3, the syringe block 7B is of two-piece construction comprising a lower block 15 and an upper block 17. The lower block 15 is provided with an elongate channel 19 which receives at least some of the body of a syringe S. The upper block 17 is also formed with an elongate channel 21 which receives at least some of the body of the syringe S. The upper block 17 thus forms a closure for syringe block 7B, with the channels 19, 21 locating the syringe in the block 7B and resisting lateral and vertical movement of the syringe S within the block 7B. Longitudinal movement of the syringe S within the block 7B is resisted by a retainer in the form of an annular recess 23 which receives a radially outwardly extending lip or grip portion of the syringe S.

The syringe mount block 7B is elongate and engages/contains a portion of the length of the syringe body, for example around half of the length of the syringe body is contained in and held by the syringe block 7B. Blocks 15 and 17 may be half the syringe body length, in which case only 15 can be used and would be for the purpose of mounting the syringe S. For thermally insulating the syringe S blocks 15 and 17 can be the full length of the syringe body so that the entire syringe body is thermally insulated. This can be important for microfluidics as even minor thermal changes can cause expansion/contraction of the syringe body and fluid contained inside the syringe body, and thus lead to unwanted and/or uncontrolled flows.

With additional reference to Figure 3, the syringe mount 7 comprises shielding configured to shield at least part of the syringe S from the ambient environment. The shielding may comprise: a) thermal shielding configured to thermally insulate at least part of the syringe S from the ambient environment. b) air flow shielding configured to shield at least part of the syringe S from ambient air currents/flow.

The shielding is provided by the structure, configuration and materials of the syringe block 7B and in particular the lower and upper blocks 15, 17. Lower block 15 of the syringe mount 7 may be considered to be an elongate shield body, whilst upper block 17 may be considered to be an elongate shield cover configured to be mounted on the elongate shield body and retain the syringe S on the syringe mount 7.

The carriage 13 comprises a slot 25 into which a syringe plunger fitting SF is received. The syringe plunger SP in turn fits inside the plunger fitting SF. When the syringe S is mounted in the syringe mount 7, relative movement between the syringe body SB and the housing 3 is prevented. Movement of the carriage 13 thus moves the plunger fitting SF and thus the syringe plunger SP relative to the housing 3, and relative to the syringe body SB. The direction of movement of the carriage 13 and the plunger SP along the rails 11 determines whether the syringe S dispenses fluid from the syringe body SB, or draws fluid into the syringe body SB.

The carriage 13 can optionally comprise a syringe retention device 37, which in the example of Figure 1 comprises a rotatable lever which can be rotated between a clamping position in which the lever clamps the plunger fitting SF into the slot 25, and a release position in which the plunger fitting SF can be removed from the slot 25.

The combination of the syringe blocks 15, 17, and the carriage slot 25 enable the syringe S to be relatively easily mounted in the correct position on the pump 1. The syringe body SB can be pressed downwardly into lower block 15, and the syringe plunger fitting SF pressed downwardly into slot 25. Upper block 17 retains syringe body SB, and moving lever 37 into the clamping position secures the plunger fitting SF on the carriage 13.

We also propose an alternative syringe mounting arrangement. With reference to Figures 5 to 9, the alternative syringe mounting arrangement comprises a different syringe block 117B which is configured to be slidingly, and removably, mounted on the upstanding end wall 7A of syringe mount 7.

Syringe block 117B has an overall shape and profile which is the same as the end shape and profile of the end wall 7A and enclosure 9, and comprises an oblong block 119 from which an oblong lug 121 projects. The lug 121 is received in a corresponding recess 123 of the end wall 7A. Lug 121, and the block 119 are provided with a through bore 125 in which the syringe body SB is received in use. Below the lug 121 are provided a plurality of retaining means which in this example comprise upper and lower pairs of magnets 127A, 127B. As can be seen in Figure 5a, the pairs of magnets 129, 131 are vertically spaced so that upper pair of magnets 129 are above lower pair of magnets 131. Magnets 127 are configured to selectively engage with two corresponding pairs of magnets 129, 131 on end wall 7A, such that the block 117B can be retained on end wall 7A in an upper condition or a lower condition. Note that in Figure 5b, the lead screw bearing B can also be seen. As also best seen in Figure 5b, the pairs of magnets 129, 131 are vertically spaced so that upper pair of magnets 129 are above lower pair of magnets 131. The lateral spacing of magnets 129, 131 is the same as the lateral spacing of magnets 127A, 127B on block 117B. Consequently, the block 117B can be positioned in an upper condition (with reference to Figure 6) or a lower position (with reference to Figures 7, 8), by aligning lower block magnets 127B with either upper magnet pair 129 or lower magnet pair 131 on end wall 7A. In either position, the block 117B is retained on the end wall 7A. The position of Figures 7 and 8 is the normal working position. The position of Figure 6, with block 117B raised, is the syringe insertion position, with the block 117B above the remainder of the housing 2, to allow easy access to, and mounting of the syringe S. Block 117B is provided with four magnets, such that when in the normal working position, each magnet on block 117B aligns with a respective magnet 129, 131 on the end wall 7A. This can help in securely retaining block 117B in the normal working, lower position. When in the upper position only lower magnets 127B of block 117B engage the upper magnets 129 of end wall 7A.

When the block 117B is in the upper position as shown in Figure 6, the bore 125 is spaced above the end wall 7A, and the remainder of the pump 1, and syringe body SB can be easily inserted into the bore 125 to retain the syringe S on the block 117B. The plunger SP and plunger fitting SF can then be extended so that the plunger fitting SF is directly above slot 25 in carriage 13. When so aligned, the block 117B can be pushed downwardly into the lower condition where magnets 127 are aligned with engage lower magnet pair 131. Simultaneously, syringe plunger fitting SF can be pushed downwardly into slot 25. Using this arrangement, the syringe S can be relatively easily mounted on pump 1, primarily using a single vertical movement simultaneously of both the syringe body SB an the plunger fitting SF. The syringe S is initially pre-mounted on the raised block 117B (or even on the block 117B before it is mounted on syringe mount 7), and then depressed into the lower position. In this example, the retaining means have been described as magnets, but could comprise any other suitable retaining element(s), mechanism or assembly for block 117B to movably engage with endwall 7A so as to be movable between the raised and lowered conditions. For example, the block 117B and end wall 7A could be provided with respective slots and lugs or other formations to engage the slots. Referring to Figure 5, such retaining means could additionally or alternatively comprise screw or bolt holes 140 configured to received screws or bolts that pass through block 117B, to bolt block 117B to end wall 7A.

The enclosure 9 contains the electronic components necessary for the syringe pump 1 to function. In particular the enclosure contains: a) at least one motor which is configured to drive shaft(s) 12, either directly or via an intermediate gear assembly. b) at least one electronic controller, configured to output a motor control signal to control the speed and direction of rotation of the motor. c) A user interface 27 configured to generate two signals that are input to the electronic controller i. a user interface signal indicative of the position of the user interface; and ii. a user interface speed signal indicative of the speed of movement of the user interface, when moved by the user. d) A single combined power and data connector 29, for example a USB port, configured to be connected to a combined power and data cable configured to supply the syringe pump 1 with power and/or data as required, via a single cable. e) Optionally at least one battery and/or supercapacitor to power the motor and/or to power the electronic controller and/or to power the user interface. In the example illustrated, a separate battery and/or supercapacitor may be provided which plugs into the enclosure via a power connector 29. f) Optionally one or more user displays, such as LEDs 31, which may be multicolour LEDs, and/or display panels, which may comprise one or more LCD or OLED panels 32 The display panel may be configured to be controlled to display parameters of the fluid being delivered, such as flow rate, or volume dispensed for example. g) Optionally one or more user programmable buttons 33. h) Optionally one or more cooling devices, such as one or more cooling fans. i) Optionally an external I/O port 35 for connecting the pump 1 to pump accessories. j) Optionally a sound emitter such as a beeper or speaker to provide audible warnings/audible feedback or other audible information to the user.

The user interface 27 in this example is an electro mechanical actuator configured to convert a mechanical movement of the actuator by the user into an electronic control signal sent to the electronic controller.

In this example the user interface 27 is an electro-mechanical continuous rotary encoder attached to a control knob which can be rotated relative to the housing 3. Rotation of the control knob may be smooth rotation, or may provide feedback to the user as it is rotated, for example by clicking or vibrating. The user interface 27 could comprise an electronic rotary controller for example as could be provided on a touch sensitive region or a touch screen display. Further, the rotary interface could instead comprise a linear interface in which the user moves the interface, or their finger relative to the interface, in a straight line. It is envisaged that the user interface could comprise any interface in which a signal can be generated indicative of relative movement between the interface and the housing, or between the interface and the user.

The needle or nozzle of the syringe S can be connected to one end of tubing, the other end of which is connected to any desired component or apparatus configured to receive fluid from the syringe S. In one example the tubing can be microfluidic tubing that connects the syringe S to one or more microfluidic chips MC. An example chip MC can be seen in Figure 2. Chip MC could of course take any desired structure and configuration provided the chip is configured to receive fluid from the syringe S, optionally via connecting tubing. Example tubing for such a microfluidic chip can be about 0.8mm to 1.6mm external diameter and 0.125mm to 1mm internal diameter. An aspect of this disclosure relates to advantageous geometric and physical configuration features of the housing 3. These include that the housing 3: a) is generally oblong being longer than it is wide and comprises a longitudinal axis along which the actuator moves. b) has a length, the length being in the range of 150-250mm, or 175 to 225mm, or 185 to 205mm. c) has a width: the width being in the range of 30 to 70mm, or 40 to 60mm, or 45 to 55mm. d) has a width, the width being less than three times the diameter of the syringe body. In microfluidics, typical syringes can range from 10pL to 2.5ml_. Typical syringe diameter can therefore be from around 6mm external diameter to 12mm external diameter. e) has a height, the height being in the range of 30 to 70mm, or 40 to 60mm, or 45 to 55mm. f) has a height, the height being less than ten times the diameter of the syringe body. g) comprises a planar base and a planar top surface spaced from the planar base, the base and top surface being configured such that the syringe pump can be vertically stacked with another syringe pump. h) comprises a pair of opposed planar sides that are configured to allow the syringe pump to be horizontally stacked with another syringe pump. i) comprises a footprint of less than 15000 mm² , or less than 12000 mm²', or less than 10000mm².

Further, the housing: a) defines a notional envelope defined by the uppermost, lowermost and lateral most parts of the housing 3, the carriage 13 being contained within the envelope. b) has a width, the carriage 13 not laterally projecting beyond the width. c) has a height, the carriage 13 not vertically projecting beyond the height.

The above features, or combinations of any one of them, enables the syringe pump 1 to be relatively compact, and facilitates using a plurality of syringe pumps 1 to be used together in close proximity, whether or not vertically or laterally stacked. At the least the syringe pumps 1 are configured to be stacked in at least one direction, for example laterally. The syringe pumps 1 are configured to be stacked together so that the housings 3 are in contact along their length. When so placed, the carriage 13 of each pump 1 can still move without interfering with the adjacent pump(s). For relatively large syringes (as might be used for non-microfluidic applications) there may be extensions beyond the housing 3 of the pump in the vertical direction, but the pumps 1 would still stack side-by-side irrespective of syringe size.)

Most syringe pumps on the market are designed to operate on a lab bench, and to utilize a variety of syringe sizes ranging from small (100s of uL where 5 pL is typically the smallest;) to large (10s of ml_). They typically have relatively large footprints so that they cannot be stacked closely together as is often required when working with short tubing attached to small microfluidics devices. Syringe pump 1 has a relatively small footprint and a relatively long and thin housing 3 which enables multiple pumps 1 to be placed in close proximity with each other and with a microfluidic chip MC (see for example a three-pump layout in Figure 2). Because of the relatively short tubing connections, fluid delivery is rapid as the fluid distance is relatively short, and there is less wastage of potentially expensive sample due to the reduced ^' dead volume' of fluid inside the short tubing.

Most syringe pumps require two or more cables in order to operate in an automated mode to perform automated pump operations. The first cable is required to provide power for the motor and electronics, and a second cable is required to provide data communications between the pump and a computer. With syringe pump 1, the motor and electronic controller are sufficiently low powered to allow operation from, for example, a single USB cable plugged into a computer. This is useful from a usability point-of-view because it reduces cable clutter and simplifies the overall experimental apparatus, for example where the syringe pump 1 comprises part of an apparatus used in a laboratory or the like. Syringe pump 1 can provide greater flexibility as each pump 1 can be stacked next to another, or each pump 1 can be orientated in a manner that places them in an optimal position that is not forced by stacking. Furthermore, reducing the number of cables reduces the potential for mechanical vibrations to be passed along the cables. Mechanical vibration should be eliminated for many microfluidic experiments and can be caused by motors and fans inside other instruments that pass on their vibrations via mechanical coupling (e.g. cables) to the syringe pump 1 and then through the connecting tubing and on to the microfluidic chip.

Syringe pumps are typically powered from a mains power supply. This requires some form of AC-DC transformer, often known as a power brick, or AC. mains plug and wiring. Syringe Pump 1 is designed to be relatively low powered and thus can be powered from a single USB port on a computer, or a USB phone charger, or a USB battery pack such as a Lithium-Ion battery pack or an internal battery or super capacitor. For example a standalone off the shelf portable power bank comprising a battery for charging mobile phones could be used. The non necessity of mains electricity and power bricks simplifies the work space, for example in a confined laboratory. Standalone battery operation enables the syringe pump 1 to be used in places where mains is not available such as inside incubators or in remote out-of-lab locations. Battery operation can also be useful for some scientific experiments that are sensitive to mechanical vibrations. Vibrations can be coupled into a microfluidic experimental apparatus through syringe pump cables that are attached to other pieces of equipment which in turn contain sources of vibration such as motors and fans. Standalone operation in which the syringe pump 1 is attached to, or comprises, a battery pack or supercapacitor, decouples the microfluidic apparatus from sources of mechanical vibration.

Many microfluidic experiments require extreme stability. Stability can be interrupted by inadvertent heating or cooling the glass syringe body due to expansion or contraction of the syringe body and heating or cooling of the fluid inside the syringe S. Heating and cooling can arise from sources such as a human operator unintentionally breathing warm breath upon the syringe body, or by temperature variations in air currents due to air conditioner cycling, or other nearby pieces of equipment such as cameras that cause convection currents. Syringe pump 1 is less susceptible to disturbed fluid flows in the ambient environment due to air temperature fluctuations, by shielding the glass syringe body from external air currents by using shielding in the form of a sleeve 15, 17 around the syringe body as described above, with reference to Figure 3. Many syringe pumps have complex user controls and require an extensive user manual/training to operate. Syringe pump 1 follow a ^' less is more' or ^' it just works' philosophy such that instructions for basic standalone (non-computer) operation can be explained relatively easily. Syringe pump 1 enables the introduction of flexibility to the syringe pumps (e.g. automation, pumping on/off, ramping profiles) by defining these on a computer and downloading them onto (or at least using them to control) the pump 1.

Syringe pump 1 provides an improved solution for controlling the metering of fluid from the syringe S. Such metering could involve control of fluid injection flow rate and/or fluid volume dispensed.

As described above syringe pump 1 comprises a user interface 27, movably mounted on the housing 3, and configured to generate a control signal by moving the user interface 27. The control signal is indicative of both the position of the user interface 27 (relative to a predetermined range of possible positions of the user interface 7), and the speed of movement of the user interface 27 when moved by the user. The control signal is sent to the electronic controller, the electronic controller generating a motor control signal in dependence upon both the position of the user interface, and the speed of movement of the user interface when moved by the user; and also the direction of movement of the user interface 27.

The user interface 27 is configured such that:

• the speed of movement of the user interface, along with its position, determine the resulting speed of movement of the carriage 13 and thus the flow rate of volume dispensed. If the user interface is moved quickly, and/or by a large movement, the carriage moves quickly, if the user interface is moved slowly, and/or by a small movement, the carriage moves slowly. For example, when the carriage moves slowly, the lead screw 12 may take an hour to complete one full revolution. When moving quickly, the lead screw 12 may rotate sufficiently quickly that the carriage 13 moves from one end of the lead screw 12 to the other in less than five seconds. • the direction of movement of the user interface 27 determines the direction of the subsequent movement of the carriage 13 when the current state is neutral, as in Figure 12.

• the user programmable buttons 33 can be used to set a desired speed and direction of movement of the carriage 13. For example, if the user interface 27 is moved a certain amount in one direction, this moves the carriage 13 at a certain speed in a first direction. Pressing and holding down a button 33 can be used to save this speed and direction of movement such that depressing that button 33, or a different button 33, switches the motor on and off, but when switched on, the motor moves the carriage 13 at the speed and direction determined by the initial input to the user interface. At least a pair of buttons 33 may be provided.

When so programmed, one button 33 can cause the carriage 33 to move in one direction at the programmed speed, whilst the other button 33 can cause the carriage 33 to move in the other direction at the programmed speed. LEDs 31 can activate/deactivate accordingly, for example to indicate to the user that the desired speed and direction has been successfully programmed.

Software backlash removal

As described above, the carriage 13 comprises an anti-backlash nut (not shown on the drawings, but located inside the carriage 13). This should ideally remove all backlash, however in reality that may not be the case. Backlash can occur as the carriage 13 is controlled to change direction. When the motor receives a control signal to change direction, the motor stops rotating in a first direction and begins rotating in the opposite direction. However, when the motor stops rotating in one direction and starts rotating in another direction, there may be a delay before the carriage also stops moving in one direction, and changes direction so as to move in the opposite direction, primarily due to the inevitable slack in the engagement between the carriage 13 and the lead screw 12.

We propose an alternative or additional means to manage backlash, using a software algorithm. The algorithm works is as follows: when the lead screw 12 is rotating in the clockwise direction, and we want to stop the rotation and then move into an anticlockwise direction, ideally the lead screw/anti-backlash mechanism should have zero backlash in that the carriage 13 will immediately follow the lead screw 12 in changing direction exactly as the lead screw 12 changes direction. In reality it may take one or more micro-steps of the stepping motor before the lead screw 12 and backlash nut fully engage. In this case, if we measure how many micro-steps are needed to entirely remove the backlash then we can use the software algorithm to add those micro-steps each time a change of direction takes place. Thus, the algorithm is programmed with how many micro-steps take place before the carriage 13 changes direction, this information can be used to generate a compensation signal which is used to control the motor to allow for those micro-steps.

Wi-Fi and Bluetooth wireless capability

To control the syringe pump 1 wirelessly, the pump 1 can be configured to include a wireless transceiver configured to transmit and receives signals with a remote electronic device. For example, the enclosure could be provided with a Bluetooth and/or Wi-Fi module so that the pump(s) 1 can be controlled via a computer/tablet/phone device's touch screen or keyboard.

Heating the sample inside the syringe

As described above, the syringe body is thermally insulated when mounted on the pump 1 in order to stop unwanted air currents from reaching the body of the syringe S and changing the flows. We also propose wrapping a heater element around the syringe S in order to heat the sample for cases where the sample is biological and needs to be held at say 37°C. Any type of heater element or elements may be provided, extending along all or part of the syringe S, and may be controlled by the electronic controller in the enclosure.

Programming

Syringe pump 1 has a relatively minimal user interface. If more complexity is required in terms of the operation and driving of the syringe S, then that can be provided through a computer interface configured to communicate with the electronic controller of the pump 1. Thus if the end user wants, for example, pulsed flow or ramping or sinusoidal flows, then the user can define said flows on the computer interface, optionally remotely from the syringe pump 1, and download them to the syringe pump 1, or at least generate a control signal that is received by the syringe pump 1. Thus, the user could program the pump 1 in a laboratory, or remotely, with some relatively complicated flows, and then take the pump 1 out into a more remote environment, without a computer.

With reference to Figure 10, the electronic controller is configured to generate an intermediate variable being a user interface speed signal, shown as an a-value in Figure 10, in dependence upon processing of both the speed of the user interface 27 when moved by the user, and a predetermined and prestored relationship between the a-value and the speed of movement of the user interface. The electronic processor is configured to select the a-value that corresponds to the measured speed of movement of the user interface in the predetermined and prestored relationship. The relationship between the a-value and speed of movement of the user interface 27 may be stored in a memory of the electronic controller, or may be stored remotely and transmitted to the electronic controller, for example, via data connector 29, or wirelessly via a transceiver of the syringe pump 1.

With additional reference to Figure 11, the electronic controller is subsequently configured to generate the motor control signal in dependence upon a predetermined relationship between the motor speed and the position of the user interface 27, wherein the motor control signal is based on a function of the selected a-value for different user interface positions. The motor control signal is effectively a signal that the controller uses to control the motor to move the plunger of the syringe S to dispense the desired volume or flow rate of fluid. In this example, the desired fluid is characterised by a flow rate. The motor control signal in this example is thus indicative of a desired fluid flow rate.

Syringe pump 1 is configured to perform both coarse and ultra-fine control of the flow rate provided by a syringe pump. The electronic controller is controlled by an algorithm having the two inputs, both related to the electro-mechanical user interface 27 situated on the housing 3 of the syringe pump 1: i. user interface position input ii. user interface rotation speed input

The output is a target flow rate which the syringe pump 1 should provide. An intermediate value (referred to as the a-value as described above) is used in the calculation process and is based on the user actuation rotation speed input (input 2). Figure 10 demonstrates an example of how the a-value is computed, while Figure 11 demonstrates an example of how the flow rate is calculated based on the two inputs.

Figure 10 shows calculation of a-value based on current user interface rotation speed. The speed is measured multiple times per second, and the a-value is recalculated for each time interval. The user-definable limits minimum a-value and maximum a-value define the finest/coarsest possible adjustment curves according to the equation shown in Figure 5.

Figure 11 shows generation of flow rate adjustment curves. A family of exponential flow rate adjustment curves are specified according to the equation, with each curve in the family providing a means of adjusting the flow rate with a different degree of precision. Only one of these curves is selected at a time; depending on which one is selected, adjustment precision may range from coarse through to ultra-fine. The inputs used to specify the exact curve selected at a given point in time are the user interface position and the a-value, which is in turn calculated from the user interface speed as described above. The use of flow rate adjustment curves which are non-linear in nature and are described by two measured variables (the position and speed of user interface 27) provides a way for the entire range of flow rates which may be provided by the syringe pump 1 to be selected quickly and precisely. Coarse adjustment allows the flow rate to be changed faster at the expense of precision; ultra-fine adjustment allows the flow rate to be selected with higher precision but at the expense of adjustment speed. With reference to Figure 10, increasing the rotation speed of the user interface (from i to ii) at a certain point in time (point A in Figure 11) results in an increase in the coarseness of the adjustment curve. This is demonstrated in Figure 11, where the middle line deviates from the original curve (dashed) after point A. Essentially, the user interface provides a means for the user to dynamically trade-off precision for speed and vice-versa, simply by changing the speed at which they interact with the interface.

With reference to the flow rate adjustment curves depicted in Figure 11, these may be exponential (as described), or alternatively may be generated according to some other non-linear function of the current position and current speed of the user interface 27. Optionally, in addition to this primary mode of operation, the interface may provide secondary modes of operation, where the motor control signal is generated according to only one of either the position or speed of the user interface. Yet another secondary mode of operation may not require the use of a non-linear flow rate adjustment curve at all; the flow rate may be directly proportional to either the position or speed of the user interface, or some combination thereof.

The electronic controller is configured to measure the speed of movement of the user interface 27 when moved by the user multiple times per second. We reiterate here that this speed of movement could be a relative speed between an electro mechanical interface 27 and the housing 3 (for example if the interface 27 is a control knob or dial or the like), or could be relative movement between the user and the interface (for example if the interface 27 is touch sensitive interface).

I/O port 35 is configured to provide an electrical input on the syringe pump 1. Electrical input 35 is configured to enable the following example functionality, using pump accessories that are configured to be connected to the I/O port 35 and supplement the functionality of the pump 1. The accessories can be controlled by the electronic controller of the pump 1, and can provide output signals that are received and processed by the electronic controller. Example functionality is as follows:

• flow sensing (this is used in microfluidics to control flow in a closed loop fashion).

• temperature sensing, particularly of the ambient environment in which the pump 1 is used, be this inside a building or out in the field (for example a 37 °C incubator temperature, or ice temperature when the pump 1 is used in the field); • voice control with commands such as "start", "stop", "increase flow by 10%" etc.

• joystick input (used for various scientific devices such as motorized microscope stages).

• one or more accelerometers and/or tilt sensing - this is used to control flows by tilting a control lever to control flow rates. Such sensors could also provide an indication of how still the pump 1 is in use, and/o whether there has been any disturbance of the pump 1 in use, that might affect operation. Movement of the pump 1, or lack of, can be particularly important in microfluidics.

• one or more electro-mechanical switching valves for refilling the syringe S.

The electronic controller is configured to delay any movement of the syringe carriage 13 when the user interface is moved from one direction to another, that is when the user is intending to change the direction of fluid flow through the syringe S. The delay may be between 0.2 and 2 seconds

In addition to the flow control algorithm of Figures 10 and 11 above, support for operating the pump 1 in multiple directions is also provided. This is achieved by detecting the direction of relative movement of the interface 27, for example whether the user interface 27 is being rotated in a clockwise or anticlockwise direction. There are three states defined, referred to as forward, backward, and neutral. When in the forward state, fluid is being expelled from the syringe S. When in the backward state, fluid is being drawn into the syringe S. The flow is otherwise stopped. This can be seen with reference to the flow control state diagram of Figure 12. Note that for brevity in Figure 12, inputs resulting in a transition back into the same state as is currently selected have been omitted. For instance, rotating the user interface 27 while in the forward or backward states will, in general, result in the flow rate being increased or decreased in accordance with Figures 10 and 11, without a corresponding change of state.

When in neutral, rotating the user interface will cause a transition into the forward or backward state. When in either of these states, flow control is achieved as previously described. If the flow rate is reduced to its minimum value (set as a programmable limit), the syringe pump 1 transitions into a delay state. This is achieved either by rotating the user interface anticlockwise when in the forward state, or clockwise when in the backward state, until the minimum flow rate is reached (corresponding to a user interface position of 0 in Figure 11). After a relatively short delay (e.g. 0.5 seconds), the pump will transition into the neutral state. This delay only begins once the user interface 27 becomes stationary. While in the delay state, this delay will be continually reset whenever the user interface 27 is rotated further. Therefore, the user interface 27 must remain stationary for the entire delay period before the transition into the neutral state occurs.

This safety feature prohibits the user from accidently changing the pump direction when making relatively large adjustments to the flow rate. The pump 1 must transition into neutral for a minimum of the delay period before changing direction.

The user interface comprises the only actuator that is required to control the flow rate and/or volume of fluid dispensed. The user interface has been described above as a rotary actuator. However linear actuators are also envisaged, or any other user interface being an electro mechanical actuator configured to convert mechanical movement of the user interface by the user into an electronic control signal, or any other electronic actuator such as any one or more of a touch sensitive actuator, tilt sensor, voice control, foot switch, joystick.

Pump 1 could be sold and/or used as a kit. The kit could comprise any one or more of the following:

• multiple pumps 1

• a syringe S

• a plurality of syringes S, optionally of different sizes

• a battery pack; internal battery; and/or supercapacitor.

• a sensor for connection to I/O port 37

• tubing for connecting the syringe(s) to a component that receives the fluid

• one or more microfluidic chips

The housing 3 may comprise a plurality of feet to space the housing base 5 from the floor or benchtop. the feet may be anti-slip and/or anti vibration feet. Whilst a carriage 13 has been described mounted on a pair of laterally paced rails 11 and a single lead screw 12, any other means of movably mounting the carriage 13 on the housing 3 could be provided. For example any number of rails 11 and lead screws 12 could be used. The carriage 13 could be partially received in an elongate slot or channel in the housing base 5, with a single lead screw driving the carriage 13 along the channel.

Syringe pump 1 allows the user to relatively precisely and quickly adjust the motor speed across a relatively wide speed range using a continuously rotating knob on the pump. The knob is used to control the syringe actuation rate (which is the fluid delivery rate from the syringe). The knob and software control algorithm provide what is required for microfluidics which is relatively precise low-delivery-rate control and relatively high-delivery-rate control through a very simple control knob. The continuously rotating knob attaches in software to a mathematical function that determines the speed of the motor as a function of the knob position and velocity. This provides an improved user experience for the unique conditions encountered in many microfluidic experiments.

The above described precise and rapid control of the motor speed, across a wide speed range, can for example be useful in "priming" of microfluidic chips. Typically, prior to performing an experiment, fluids need to be inserted from one or more syringes into the microfluidic channel(s) of the microfluidic chip. This can be difficult to do in the absence of the necessary controls on the pump or PC software interface. The problem can be two-fold: loading the fluids into the microfluidic channels, and getting rid of bubbles. The latter can be a particularly difficult issue to overcome in microfluidics.

Loading the fluid requires both slow and fast syringe fluid delivery as the tubing can take a long time to fill (requiring relatively fast fluid delivery) and once almost completely delivered requires careful management and movement of the fluid(s) inside the microfluidic chip (thus needing slow). The controller described above enables relatively quick and intuitive access to a wide range of speed variations, and also enables extremely slow speeds for finalizing the fluids on- chip at the end stage of fluid delivery to the microfluidic chip. The programmable buttons 33, which can be programmed for both slow and fast or intermediate speeds, and the software which can control fluid delivery across the full range help to achieve this two stage fluid delivery control, during priming of the microfluidic chip.

Removing, or at least minimising, bubbles in the fluid once delivered to the microfluidic chip can also be a significant issue. They are often too small to see, or they are not visible inside a piece of non-transparent tubing, or they are sticky and thus adhered to surfaces such as tubing surfaces, microfluidic chip surfaces (plastic or glass), or non-continuous surfaces such as found in connectors where the mating surfaces are not sufficiently smooth due to a join or the like. To get rid of bubbles, it is possible to use a supplementary de-gassing device, but this adds more complexity (and cost) to experiments.

The above described syringe pump 1 includes a "hammer flush" function in which the pump 1 is controlled to inject a relatively short but relatively high-flow-rate pulse of fluid into the microfluidic chip, which knocks the bubbles from the surface and allows them to be flowed out from the chip. This can be useful in many experiments, to minimise spongy flow behaviour of fluids due to "soft / springy" air bubbles which can make the fluids difficult or even impossible to work with. The fluid pulse described above can be useful in removing bubbles, and/or as a method for cleaning sticky particles from inside microfluidic devices.

Temperature sensor logging / failure detection

The syringe pump 1 may be provided with one or more sensors configured to detect ambient conditions such as temperature, pressure, or humidity for example. For example, where the syringe pump 1 is provided with a temperature sensor, this temperature sensing capability allows the ambient temperature around the syringe pump to be measured and logged. This data can be used to provide supplementary data in experiments, and/or for detecting fault conditions. For example if heating or cooling equipment or environmental conditions were to change unexpectedly or to go outside an expected temperature range, this would be detectable and could be logged by the pump controller. End position detection

The syringe pump 1 may be configured for carriage end position detection, for example by provision of one or more suitable sensors at each end of the carriage 13, or each end of the stroke of the carriage 13. Such sensors could comprise contact, proximity or light sensors for example. End position detection allows the extreme positions of the carriage 13 to be determined, that is, when the carriage 13 runs into, or is at least adjacent, either end wall 7A or housing 9. The syringe pump 1 is configured to use smart electronics to detect a collision event, such that the carriage 12 is stopped before the collision event occurs, without any user intervention. Measuring the extreme positions of the carriage 13 can also allow an absolute carriage position datum to be set which can be used for other advanced features such as auto positioning of the carriage 13 for example.

Torque limiting

The syringe pump 1 can be provided with a torque limiter. Torque limiting allows the torque at which the motor stalls to be controlled, thus limiting the force that can be applied to the syringe S. This can be useful in a microfluidic context in which relatively small syringes are used which can generate relatively large pressures (due to pressure being the applied force per area). Torque limiting is thus a safety feature that allows the pump 1 to limit the damage that relatively high pressures could do to devices attached to the syringe's tubing.

Shaft positioning and stall detection

The syringe pump may be provided with a shaft position sensing arrangement. Shaft position sensing is a feedback technique that allows the pump 1 to determine whether the lead screw 12 is rotating as expected. If the lead screw 12 is not rotating for some reason when it ought to be, for example if it has stalled, then that stalled condition can be detected and an alert (such as an audible or visual warning) generated for the user. Prior art methods of determining rotational position of a shaft typically used encoders on the shaft. Such a technique could be used here. However, pumps in accordance with this disclosure are relatively small by comparison and thus such encoders would not easily fit. The controller makes an assumption that when the motor is instructed do a step, it does a step. However, this may be false and the motor may stall and/or miss steps. We cannot detect small step losses in isolation as the combination of the magnetic sensor on the PCB and a magnet mounted on the rotating shaft (lead screw 12) do not provide sufficient resolution for the relatively small angles involved (e.g. micro stepping is 360 degrees / (400 * 256) steps which is about 100,000 micro steps per revolution of the lead screw 12). Missing steps can be detected if they accumulate sufficiently because there will be a significant difference between the sensed shaft angle and the angle that the controller thinks the shaft should be at.

To determine the absolute (rather than relative) position of the carriage, the carriage can be crashed into the end of the pump body. The crash incident provides a signal that the software then uses to set a datum (say, position = 0) and then a counter is used to assume that the shaft is at a specific "relative" position, relative to the initial datum.

For microfluidics, the loss of steps can be an advantage in some applications as noted in the "Torque limiting" section, as this provides a "slipping clutch". We can control the torque at which the clutch slips via software, thus protecting attached microfluidic devices.

Most syringe pumps are made from many mechanical and electrical parts. Syringe pump 1 is relatively simple in comparison, consisting of approximately twenty parts to build the entire pump (PCB = 1 part). This makes manufacture of the pump relatively simple and consequently has fewer parts that are susceptible to failure.

Unless the context clearly requires otherwise, throughout the description, the words "comprise", "comprising", and the like, are to be construed in an inclusive sense as opposed to an exclusive or exhaustive sense, that is to say, in the sense of "including, but not limited to".

Although this disclosure has been described by way of example and with reference to possible embodiments thereof, it is to be understood that modifications or improvements may be made thereto without departing from the scope of the disclosure. The disclosure may also be said broadly to consist in the parts, elements and features referred to or indicated in the specification of the application, individually or collectively, in any or all combinations of two or more of said parts, elements or features. Furthermore, where reference has been made to specific words or integers of the disclosure having known equivalents, then such equivalents are herein incorporated as if individually set forth.

Any discussion of the prior art throughout the specification should in no way be considered as an admission that such prior art is widely known or forms part of common general knowledge in the field.

Claims

1. A syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein the syringe mount comprises shielding configured to shield at least part of the syringe from the ambient environment.

2. A syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein the syringe pump comprises: a user interface, movably mounted on the housing, and configured to allow the user to interact with the user interface via relative movement between the user interface and the housing or relative movement between the user interface and the user, and configured to send a signal to the electronic controller indicative of both the position of the user interface, and the speed of movement of the user interface; the electronic controller generating a motor control signal in dependence upon both the position of the user interface, and the speed of movement of the user interface.

3. A syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein: the housing defining an envelope defined by the uppermost, lowermost and lateralmost parts of the housing, the actuator being contained within the envelope.

4. A syringe pump configured to dispense fluid from a syringe comprising a hollow syringe body and a plunger movable within the syringe body, the syringe pump comprising: a housing, the housing containing a motor and an electronic controller; a syringe mount configured to mount the body of the syringe on the housing to prevent relative movement between the syringe body and the housing; an actuator movably mounted on the housing relative to the syringe mount, and configured to engage the syringe plunger such that movement of the actuator drives the syringe plunger into or out of the syringe body, the actuator being driven by the motor, the motor being controlled by the electronic controller; wherein: the housing is generally oblong being longer than it is wide and comprises a longitudinal axis along which the actuator moves; wherein the width of the housing is less than three times the diameter of the syringe body.

5. The syringe pump of any one of claims 1, 3 or 4, comprising a user interface, movably mounted on the housing, and configured to allow the user to interact with the user interface via relative movement between the user interface and the housing or relative movement between the user interface and the user, and configured to send a signal to the electronic controller indicative of both the position of the user interface, and the speed of movement of the user interface; the electronic controller generating a motor control signal in dependence upon both the position of the user interface, and the speed of movement of the user interface.

6. The syringe pump of claim 2 or 5 wherein the electronic controller is configured to generate a user interface speed signal in dependence upon processing of both the speed of the user interface when moved by the user, and a predetermined and prestored relationship between the user interface speed signal and the speed of movement of the user interface, wherein the electronic controller is configured to select the user interface speed signal that corresponds to the measured speed of movement of the user interface in the predetermined and prestored relationship.

7. The syringe pump of claim 6 wherein the electronic controller is configured to generate the motor actuation signal in dependence upon a predetermined relationship between the motor speed and the position of the user interface, wherein the motor control signal is based on a function of the calculated user interface speed signal for different user interface positions.

8. The syringe pump of any one of claims 2 and 5 to 7 wherein the electronic controller is configured to measure the relative speed of the user interface multiple times per second.

9. The syringe pump of any one of claims 2 and 5 to 8 wherein the electronic controller is configured to delay any movement of the syringe actuator when the user interface is moved from one direction to another, that is when the user is intending to change the direction of fluid flow through the syringe.

10.The syringe pump of claim 9 wherein the delay is between 0.1 and 2 seconds, or between 0.25 and 1 second, or between 0.35 and 0.6 seconds.

11.The syringe pump of any one of claims 2 and 5 to 10 wherein the user interface comprises the only actuator that is required to control the flow rate and/or volume of fluid dispensed.

12.The syringe pump of any one of claims 2 and 5 to 11 wherein the user interface is a rotary actuator.

13.The syringe pump of any one of claims 2 and 5 to 12 wherein the user interface is a continuously rotary actuator.

14.The syringe pump of any one of claims 2 and 5 to 13 wherein the user interface is an electro mechanical actuator configured to convert mechanical movement of the user interface by the user into an electronic control signal.

15.The syringe pump of any one of the preceding claims wherein the housing is generally oblong being longer than it is wide and comprises a longitudinal axis along which the actuator moves.

16.The syringe pump of claim 15 wherein the housing has a length, the length being in the range of 150-250mm, or 175 to 225mm, or 185 to 205mm. The syringe pump of claim 15 wherein the housing has a width, the width being in the range of 30 to 70mm, or 40 to 60mm, or 45 to 55mm. The syringe pump of any one of claims 15 to 17 wherein the width of the housing is less than three times the diameter of the syringe body. The syringe pump of any one of claims 15 to 17 wherein the housing has a height, the height being in the range of 30 to 70mm, or 40 to 60mm, or 45 to 55mm. The syringe pump of claim 19 wherein the height of the housing is less than 10 times the diameter of the syringe body. The syringe pump of any one of the preceding claims wherein the housing comprises a planar base and a planar top surface spaced from the planar base, the base and top surface being configured such that the syringe pump can be vertically stacked with another syringe pump. The syringe pump of any one of the preceding claims wherein the housing comprises a pair of opposed planar sides that are configured to allow the syringe pump to be horizontally stacked with another syringe pump. The syringe pump of any one of the preceding claims wherein the housing comprises a footprint of less than 15000 mm², or less than 12000 mm²', or less than 10000mm². The syringe pump of any one of the preceding claims wherein the housing defines an envelope defined by the uppermost, lowermost and lateral most parts of the housing, the actuator being contained within the envelope. The syringe pump of any one of the preceding claims wherein the housing has a width, the actuator not laterally projecting beyond the width. The syringe pump of any one of the preceding claims wherein the housing has a height, the actuator not vertically projecting beyond the height. The syringe pump of any one of the preceding claims wherein the syringe mount is elongate and engages/contains a portion of the length of the syringe body. The syringe pump of claim 27 wherein the syringe mount engages/contains around half of the length of the syringe body. The syringe pump of claim 27 and claim 28 wherein the syringe mount projects from one end of the housing. The syringe pump of any one of the preceding claims wherein the syringe mount comprises shielding configured to shield at least part of the syringe from the ambient environment. The syringe pump of claim 30 wherein the shielding comprises thermal shielding configured to thermally insulate at least part of the syringe from the ambient environment. The syringe pump of claim 30 or 31 wherein the shielding comprises air flow shielding configured to shield the at least part of the syringe from ambient air currents/flow. The syringe pump of any one of claims 30 to 32 wherein the syringe mount comprises an elongate shield body, and an elongate shield cover configured to be mounted on the elongate shield body and retain the syringe on the syringe mount. The syringe pump of claim 33 wherein the elongate shield body comprises a channel into which the syringe body can be inserted to mount the syringe to the shield mount.

35.The syringe pump of claim 33 or 34 wherein the elongate shield cover comprises a channel into which the syringe body is received.

36. The syringe pump of any one of the preceding claims wherein the shield mount comprises a retainer configured to engage the syringe body and prevent longitudinal movement of the syringe body along the longitudinal axis of the shield mount.

37.The syringe pump of claim 36 wherein the retainer comprises a radial outwardly directed recess into which part of the syringe body is received.

38.The syringe pump of any one of the preceding claims wherein the housing comprises an enclosure, spaced from the syringe mount, and containing the motor and the electronic controller and the user interface.

39.The syringe pump of claim 38 wherein the enclosure further comprises a battery and/or a supercapacitor.

40.The syringe pump of claim 39 wherein the battery and/or supercapacitor is internal of the enclosure.

41. The syringe pump of claim 40 wherein battery and/or supercapacitor is external of the enclosure, and configured to be electrically connected to the enclosure.

42.The syringe pump of any one of claims 38 to 41 wherein the enclosure further comprises a connector for connection to a power supply cable.

43.The syringe pump of any one of the claims 38 to 42 wherein the enclosure further comprises a connector for connection to a data cable.

44.The syringe pump of claim 42 or 43 wherein the enclosure where the power and data connection are the same connector, the syringe pump further comprising a single external cable, the single external cable being configured to supply both power and data to the syringe pump.

45.The syringe pump of claim 44 wherein the power and data connector is a USB connector.

46.The syringe pump of any one of claims 38 to 45 wherein the enclosure is spaced from the syringe mount along the longitudinal axis of the housing.

47.The syringe pump of any one of the preceding claims wherein the enclosure and syringe mount both project upwardly from a base of the housing.

48.The syringe pump of any one of the preceding claims wherein the syringe pump comprises less than 30 components, where the electronic controller is considered to be a single component, and preferably less than 20 components.

49. A fluid dispensing system comprising the syringe pump of any one of the preceding claims, at least one syringe, and dispensing tubing configured to be connected to the syringe.

50.The system of claim 49 comprising a plurality of syringe pumps.

51.The system of claim 49 comprising a plurality of syringes.

52.The system of any one of claims 49 to 51 comprising a microfluidic chip configured to be receive fluid from the syringe.

53. An electronic controller configured to comprise part of the syringe pump of any one of claims 1 to 48.