LIQUID MANAGEMENT IN AN OPHTHALMOLOGICAL DEVICE

Abstract

The invention relates to an ophthalmological device (99) which provides suction flushing, having an aspiration function and an infusion function, as well as a replaceable cassette (1) for such a device. It comprises an aspiration conveyor device (52) for motor-driven discharge of liquid from a surgical instrument (29) into a waste container (56). According to the invention, it also comprises an infusion conveyor device (36) for motor-driven supply of an infusion medium from an infusion container (30) to said surgical instrument (29).

Claims

1. Ophthalmological device which provides suction flushing with an aspiration function and an infusion function, comprising an aspiration conveyor device for the motor-driven discharge of liquid from a surgical instrument into a waste container, in particular in the form of a peristaltic pump or vacuum suction, an infusion conveyor device for the motor-driven feeding of an infusion medium from an infusion container via an infusion connection and a line to the surgical instrument, which infusion conveyor device is designed as a peristaltic pump for the active volume delivery of the infusion medium with a known delivery volume, and a pressure measuring device with a pressure or force sensor in the device is formed between the infusion conveyor device and the surgical instrument, by means of which an infusion pressure of the infusion medium in the device can be determined.

2. Ophthalmological device according to claim 1, wherein a control module in the device is designed such that the delivery volume of the infusion volume delivery is regulated on the basis of the infusion pressure.

3. Ophthalmological device according to claim 2, wherein the regulation is carried out under consideration of a pressure drop in the line towards the surgical instrument, wherein the pressure drop is at least partially compensated with a pressure increase in the infusion volume delivery.

4. Ophthalmological device according to claim 3, wherein the pressure drop is determined by taking into account a flow velocity of the infusion medium, which flow velocity is determined on the basis of the current delivery volume of the infusion volume delivery.

5. Ophthalmological device according to claim 1 4, wherein regions of the infusion conveyor device that come into contact with the infusion medium together with regions of the aspiration conveyor device that come into contact with the liquid are formed in a common interchangeable cassette for the device, and the device comprises an infusion drive for the infusion conveyor device and an aspiration drive separate therefrom for the aspiration conveyor device.

6. Ophthalmological device according to claim 5, wherein the pressure measuring device is designed with a flexible membrane in the cassette and the pressure or force sensor in the device.

7. Ophthalmologic device according to claim 1, wherein a control unit in the device is designed such that the determined infusion pressure of the infusion conveyor device can be adjusted to a target value by means of an automatic control, wherein an adjustment of the target infusion pressure which is dependent on the delivery rate is carried out in such a way in particular that an increased pressure drop caused by the flow velocity in the line to the surgical instrument is compensated.

8. Ophthalmological device according to claim 1, wherein said device is formed with a motor-driven height adjustment of the infusion container, and switchability for optionally bypassing the infusion conveyor means is provided by a bypass valve device.

9. Ophthalmological device according to claim 8, wherein a first hydrostatically pressure-adjustable infusion is provided by means of the motor-driven height adjustment of the infusion container via a first line towards the eye, and a second pressure-adjustable infusion, which is independent thereof, is provided with the infusion conveyor device via a second line towards the eye.

10. Ophthalmological device according to claim 1, wherein the aspiration conveyor device and the infusion conveyor device are constructed in a similar—in particular identical—manner in their design and dimensioning.

11. Interchangeable cassette for an ophthalmological device, in particular for a device according to claim 5, comprising: at least one a rigid hard part as the housing of the interchangeable cassette especially made of a hard plastic, especially a thermoplastic such as polypropylene (PP) or polyethylene (PE), at least one elastic soft part in particular an elastomer or a thermoplastic elastomer, wherein the hard part and the soft part form internal liquid channels of the interchangeable cartridge and the soft part is partially accessible from the exterior of the interchangeable cassette, and wherein regions of the soft part form peristaltic pump squeezing channels on the cassette side for conveying an infusion medium in at least one of the liquid channels, and wherein regions of the soft part form at least one pressure sensor region on the cassette side for determining a liquid pressure for the infusion medium in at least one of the liquid channels, in particular wherein at least one of the hard parts forms an integral multi-component injection-molded part with at least one soft part.

12. System consisting of an ophthalmologic device, in particular according to claim 1, which provides suction flushing with an aspiration function and an infusion function, comprising a motor drive of an aspiration conveyor device for discharging liquid from a surgical instrument into a waste container, and a motor drive of an infusion conveyor device which is designed as a peristaltic pump with a known delivery volume and is separated therefrom, for feeding an infusion medium from an infusion container via an infusion connection and a line to the surgical instrument, and a pressure or force sensor in the device by means of which an infusion pressure of the infusion medium can be determined, and of an interchangeable cassette for the ophthalmological device, comprising: at least one rigid hard part as housing of the interchangeable cartridge, at least one elastic soft part, wherein the hard part and the soft part form internal liquid channels of the interchangeable cassette and the soft part is partially accessible from the exterior of the interchangeable cartridge, and wherein regions of the soft part form cassette-side peristaltic pump squeezing channels of the infusion conveyor device for delivering the infusion medium in at least one of the liquid channels, and wherein regions of the soft part form at least one cassette-side pressure sensor region for determining the liquid pressure for the infusion medium by the pressure or force sensor in at least one of the liquid channels between the infusion conveyor device and the surgical instrument, wherein the infusion conveyor device and the pressure sensor region are arranged and designed such that a pressure drop towards the surgical instrument can be compensated by detecting a delivery volume of the infusion conveyor device and by detecting the liquid pressure in the interchangeable cassette.

13. Method for the automatic infusion pressure regulation in an ophthalmological device, in particular for a suction flushing, comprising active aspiration delivery of an aspiration liquid from an aspiration connection to the device; and active infusion volume delivery of an infusion medium from an infusion container to an infusion connection, comprising a measurement of an infusion pressure of the infusion medium in the device, and a regulation of a delivery volume of the infusion volume delivery by means of the infusion pressure, in particular wherein infusion volume delivery and aspiration delivery are each carried out by means of a peristaltic pump.

14. Method according to claim 13, wherein the regulation is carried out with compensation of a pressure drop in a line connected to the infusion connection towards the eye, wherein this pressure drop is determined on the basis of a flow velocity of the infusion medium which is determined from the delivery volume.

15. Method for the automatic control of an active infusion in an ophthalmological device for suction flushing by a control unit, comprising: a determination of an aspiration delivery rate of an aspiration of the suction flushing, a feed-forward control of an infusion delivery rate of the active infusion to compensate for the aspiration delivery rate, a determination of an infusion pressure of the active infusion in the device, and a readjustment of the pilot-controlled infusion delivery rate to achieve a desired infusion pressure, which readjustment takes place as a function of the infusion delivery rate, in particular to compensate a pressure drop in a line to a surgical instrument.

16. Method according to claim 12, wherein tuning the delivery volume and a delivery pressure of the active infusion to a characteristic value of the active aspiration with a dependence of a movement of an infusion peristaltic pump on an aspiration delivery volume and on an aspiration delivery pressure of the active aspiration, in particular wherein an aspiration vacuum is determined and a temporary increase in the infusion pressure takes place when the aspiration vacuum increases.

17-21. (canceled)

22. Ophthalmological device according to claim 5, wherein passive ripple compensation in the form of a flexible line region is formed in the interchangeable cassette between the infusion conveyor device and the surgical instrument, which ripple compensation effects a compensation of fluctuations in the delivery volume of the infusion conveyor device by means of elastic deformation of the flexible line region, and/or wherein an air bubble sensor is formed along a path of the interchangeable cassette in which the infusion medium is supplied, wherein the air bubble sensor is formed with a viewing window in the interchangeable cassette and an optical monitoring system in the device.

23. (canceled)

24. Ophthalmological device according to claim 5, wherein the infusion conveyor device is formed in the interchangeable cassette with at least one squeezing channel, which is formed at least approximately in a circular arc and is made of an elastic material, the squeezing channel cross-section of which can be squeezed in a sealing manner at at least one point by actuators on the device side—in particular by rollers—and this point can be moved along the squeezing channel, in particular wherein an unsqueezed cross-sectional area of the squeezing channel varies along the squeezing channel, in particular wherein optionally a plurality of squeezing channels are arranged hydraulically parallel and actuated phase-shifted with respect to one another.

25. Interchangeable cassette according to claim 5, wherein the soft part forms functional elements of the interchangeable cassette, which functional elements comprise at least one of: a squeezing pump region for the infusion medium in the liquid channels for volume delivery in the form of a peristaltic pump, a valve device region for varying a flow cross-section in at least one of the liquid channels, a ripple compensation region for compensating pressure and/or volume fluctuations of a liquid delivery by means of an elastic liquid channel region, and/or an aspiration valve, and the interchangeable cassette is also equipped with at least a bottle connection for the connection of a container for the supply of the infusion medium, an infusion connection for supplying the infusion medium to the ophthalmic surgical instrument, an aspiration connection for connecting at least one of the liquid channels to an ophthalmic surgical instrument, and/or a waste connection for discharging liquid into a waste container.

26. (canceled)

27. Method for regulating the infusion pressure in an ophthalmological device, in particular for suction flushing, comprising an active aspiration delivery of an aspiration liquid from a patient to the device, and an active infusion volume delivery of an infusion medium from an infusion container to the patient, with a measurement of an infusion pressure of the infusion medium and a regulation of a delivery volume of the infusion volume delivery on the basis of the infusion pressure, in particular wherein infusion volume delivery and aspiration delivery are each effected by means of peristaltic pumping, in particular wherein a compensation of delivery volume fluctuations is effected with a flexibly expandable region of a liquid channel.

Description

[0043] The method and the device in accordance with the invention are described in detail below on the basis of concrete embodiment examples schematically depicted in the drawings, wherein further advantages of the invention are also discussed, wherein:

[0044] FIG. 1 shows a first block diagram of a first embodiment of an ophthalmological device according to the invention;

[0045] FIG. 2 a second block diagram of a second embodiment of an ophthalmological device according to the invention;

[0046] FIG. 3a and FIG. 3b show a first embodiment of an example of an interchangeable part according to the invention in the form of an interchangeable cassette for an ophthalmological device in 3D views from the left and right;

[0047] FIG. 4 shows a representation of an exemplary embodiment of an interchangeable part according to the invention, which is inserted in an appropriate example of an ophthalmological device in accordance with the invention;

[0048] FIG. 5 shows a superimposed view of an embodiment of an infusion liquid delivery according to the invention;

[0049] FIG. 6a and FIG. 6b show embodiments of examples of an interchangeable part according to the invention when inserted into the machine in a sectional view;

[0050] FIG. 7a and FIG. 7b show embodiments of an example of an interchangeable part according to the invention with an embodiment of an optional ripple reduction;

[0051] FIG. 8a and FIG. 8b show an illustration of an exemplary embodiment according to the invention of an interchangeable part with an active infusion conveyor device according to the invention;

[0052] FIG. 9 shows a first example of an embodiment of an active infusion in use according to the invention;

[0053] FIG. 10 shows a second example of an embodiment of an active infusion in use according to the invention.

[0054] The depictions in the figures are for illustration purposes only and, unless explicitly stated otherwise, are not to be regarded as true to scale. Identical or functionally similar features shall, as far as practicable, be consistently marked with the same reference numerals and, where appropriate, distinguished by a letter as an index. The diagrams show the basic technical structure, which can be supplemented or modified by a person skilled in the art according to general principles.

[0055] FIG. 1 shows a possible example of a block diagram of an embodiment of an ophthalmological cassette 1 according to the invention with at least one active infusion according to the invention. In this example, it can be specifically an infusion device in an interchangeable cassette 1 of an ophthalmological device 99, with which suction flushing can be carried out. In the left half of the figure an active infusion device is shown, in the right half an aspiration device.

[0056] A container 30, e.g. an infusion bottle or an infusion bag, provides an infusion liquid, e.g. a BSS (Balanced Salt Solution) or another infusion liquid. This infusion liquid supply can, for example, be equipped with a device for checking the filling level. For example, the container 30, a drip chamber 31, a connection tube and or a cassette-internal liquid channel with a wired or wireless sensor can be monitored for emptying. When cassette 1 is inserted, connection 33 can be arranged on cassette 1 so that it can be accessed from the outside and connected to the infusion container 30 or the interposed drip chamber via a tube, for example.

[0057] As known from the prior art, the infusion liquid pressure at the bottle connection 33 of cassette 1 (or in the entire infusion system) can optionally be changed by varying the height of the container suspension by means of a height adjustment of the suspension of container 30, preferably motorized and automatic, which is symbolized here by the drive 32. However, with the active infusion according to the invention, this height adjustment is not absolutely necessary but can be provided as a switchable option and/or as additional safety or redundancy on the device according to the invention.

[0058] In the case of another embodiment of a cassette 1 according to the invention, an active infusion can, according to the invention, be carried out exclusively by means of an active liquid conveyor device 36. A pumping device, such as a peristaltic pump or another liquid delivery device in the infusion system, is designed for this purpose. With such an embodiment, an infusion valve 35 and/or a height adjustment of the infusion container 30 can optionally be dispensed with. The infusion pressure and/or the delivery volume of the infusion can be varied, in particular controlled or regulated, by appropriate control of the conveyor device 36.

[0059] Another preferred embodiment of a cassette 1 according to the invention can also have—as shown in the figure—both an infusion container height adjustment 32 and an infusion liquid conveyor device 36. Cassette 1 according to the invention can be designed in such a way that the infusion pressure can additionally be adjusted or regulated as described here by changing the height difference between the container 30 of the infusion site. In particular, a valve 35 can be designed as a bypass to the conveyor device 36. Thus, with the same cassette 1, either an active infusion pressure variation (i.e. actively initiated by the conveyor device 36) or a hydrostatic infusion pressure variation (i.e. caused by a difference in height) can be provided. In particular, if required, it is possible to switch seamlessly between these two principles—e.g. also during operation—for example according to the current requirements of the operation being performed or according to the surgeon's preferences. Special applications in which two different and independent infusion pressures are required at the same time can also be carried out with such an embodiment according to the invention by applying a first pressure-adjustable infusion by means of the hydrostatic height adjustment via a first line to the eye and a second pressure-adjustable infusion with the active infusion by means of the infusion conveyor device in the cassette via a second line to the eye.

[0060] The infusion system according to the invention can also have an infusion pressure measuring device 37, by means of which a pressure in the infusion system can be determined, monitored and/or regulated. Preferably, this infusion pressure measuring device 37 is arranged after the infusion valve 35 and/or the pumping device 36, so that their determined pressure corresponds to that which is supplied to the eye. Since the infusion system can (or at least should) only have overpressure in relation to the atmosphere, this infusion pressure measuring device can be designed in such a way that only overpressure can be determined with it, and not necessarily underpressure (although such a variant would also be applicable). One of many possible examples of a concrete embodiment can be formed, for example, with a part of the infusion liquid channel that has been extended to form a pressure chamber and has a flexible membrane on the outside. When cassette 1 is inserted, this membrane is in contact with a sensitivity surface of a force or pressure sensor in the device 99. The force exerted on the membrane by an overpressure in the liquid channel relative to the atmosphere can thus be determined as a measured value for the overpressure in the liquid channel.

[0061] The infusion liquid is provided by means of the cassette 1 according to the invention with active infusion according to the invention with adjustable pressure and/or delivery volume at an external infusion connection 38 of the cassette 1, which can be connected to a line or a tube to the surgical intervention tool, e.g. the surgical handpiece 29, so that the infusion into the eye can be provided with adjustable and/or regulatable pressure and/or volume. In order to guarantee safety, the actual prevailing pressure of the infusion to the patient can be monitored with a corresponding pressure sensor 37. If necessary, pressure losses in the line system to the patient can also be taken into account—especially pressure losses due to dynamics, since the delivery volume and thus also the flow rate of the infusion are known according to the invention by the conveyor device 36.

[0062] In particular, the infusion liquid, for example, can be provided by means of the cassette 1 according to the invention with active infusion according to the invention with adjustable delivery volume via a volume conveyor device with a defined, known delivery volume at an external infusion connection 38 of the cassette 1, which connection can be connected with a line or a tube to the surgical intervention tool. In order to provide the infusion into the eye with adjustable pressure, the actual prevailing pressure of the infusion towards the patient is monitored with a corresponding pressure sensor 37 in the device. According to the invention, pressure losses in the line system to the patient can also be taken into account, especially pressure losses due to dynamics, since, according to the invention, the delivery volume and thus also the flow rate of the infusion in the line is known through the conveyor device, on which flow rate a difference between the pressure value at different ends of the line depends in a known way. Especially if a tube diameter, a tube cross-section and/or a tube length of the line are known—which is usually the case with such interchangeable cassettes or sets—a resulting pressure on the eye can be well regulated under consideration of the delivery volume. In particular, with such a direct control of the delivery volume, taking into account the pressure losses in the line, a direct and thus very fast pressure control can be achieved, which has advantageous dynamic characteristic values for this application.

[0063] According to a partial aspect of the invention, the arrangement and formation of the liquid channels within cassette 1 is preferably such that when the liquid channels are filled with liquid, this filling always takes place (at least substantially) from bottom to top—with which any air bubbles (corresponding to the medium density ratio) are displaced upwards and discharged away from the patient and an accumulation of air bubbles is avoided. Such a filling of the liquid channels of cassette 1 takes place especially after the insertion of cassette 1 when it is put into operation. For example, according to this aspect of the invention, the arrangement of the connections can be designed from bottom to top in the following order: waste bag 55—aspiration-A from patient 12a, 50—optional aspiration-B 12b—infusion to patient 38—infusion bottle 33.

[0064] The cassette 1 according to the invention can have at least one air bubble sensor 34 in the infusion system, with which a correct function can be monitored and an infusion of air can be avoided. The air bubble detector 34 can work in particular optically—for example due to different light refraction properties of air and liquid, or also on other principles, with which a distinction can be made between the presence of gas or liquid in the infusion system. For example, the principle of different angles of total reflection of liquid compared to air, different light conduction properties of liquid and air, or another active principle, such as a capacitive one, can be used. One example of a concrete embodiment can be formed with a viewing window into the liquid channel that is optically transparent at least in the wavelength used, which can be implemented in an outer shell 41, 42 of cassette 1. In one embodiment, for example, the outer shell can be made of transparent material.

[0065] Also shown here is an optional path according to the invention from the infusion system to the aspiration system of cassette 1, which can be released with a venting valve 39. This can be used, for example, to fill the aspiration system with liquid, especially when cassette 1 is put into operation, and/or to backflush infusion liquid through the aspiration system, for example to loosen occlusions (reflux) or generally to reduce the negative pressure in the aspiration path, e.g. if the physician wishes to reduce the desired negative pressure via the foot switch. For these functionalities, further valves may be available in the cassette for the corresponding switching of the liquid flows.

[0066] The aspiration system of the cassette 1 according to the invention is connected to the surgical intervention tool 29 via an aspiration connection 50 with a pipe or tube. Again, at least one air bubble sensor 34b can be present in the aspiration system. The figure also shows an aspiration valve 51. In the aspiration system, a pressure measurement can also be carried out with a pressure measuring device 10, which can, however, measure both negative and positive pressures with respect to the atmosphere. In order to detect forces in both positive and negative directions accordingly, the pressure measuring membrane of the cassette must be connected to the corresponding pressure measuring sensor in the device to transmit both positive and negative values. Examples of such known pressure detection devices can be found, for example, in patent application EP 16197018 filed on the same day by the same applicant, which is hereby included by reference, or possibly also in the references cited therein.

[0067] To achieve the aspiration effect, the figure shows two variants, i.e. on the one hand a peristaltic aspiration and on the other hand a Venturi aspiration. An embodiment of a cassette 1 according to the invention may either exhibit only peristaltic aspiration, or another embodiment of cassette 1 according to the invention may comprise only Venturi aspiration, or another embodiment according to the invention may comprise both peristaltic aspiration and Venturi aspiration.

[0068] In Venturi aspiration, the aspiration effect is caused by an air vacuum, which is usually generated by a name-giving Venturi nozzle or a vacuum pump. These variants are symbolized here by the Venturi valve 57 and the vacuum system 58. In particular, a so-called “Clean Venturi” system can also be applied, which is described in the international application EP 16196998 filed on the same day by the same applicant and is hereby included by reference. In the case of Venturi aspiration, a measured value of the aspiration vacuum in particular can be used as the basis for controlling the active infusion conveyor device 36, e.g. as described below. In particular, the active infusion conveyor device 36 according to the invention can be controlled and/or regulated on the basis of currently prevailing infusion pressure and currently prevailing aspiration vacuum by a control unit provided for this purpose. Optionally or alternatively, the control unit can also include values of a current delivery rate of the infusion and/or aspiration.

[0069] In peristaltic aspiration, a liquid conveyor device 52 is used to generate the aspiration effect. The delivery device 52 can in particular be a peristaltic pump, but optionally a membrane pump or other liquid delivery devices can also be used. The aspirated liquid is preferably pumped into an appropriate waste container 56, which is preferably connected to an appropriate waste connection 55 outside cassette 1. Again, a pressure sensor 37c, especially for overpressure, can be used to detect a pressure increase with a full waste bag.

[0070] Cassette 1, in accordance with the invention, may also have a coding 70, in particular mechanical and/or optical, which can be recorded and evaluated by a corresponding reading unit 71 of the device 99. This coding can be used to prevent multiple or non-sterile use, for example with disposable cassettes, and a specific embodiment of the inserted cassette and its optional functionalities etc. can be detected by the device 99.

[0071] In special vitrectomy procedures, when the vitreous body is removed, a gas, usually room air cleaned with a bacteria filter from the OR, is first pumped into the eye, usually with an overpressure of approximately 20 to 120 mmHg. As a result, this pumped-in air is then replaced by a silicone oil, which presses the detached retina back onto the choroid so that it can grow back again. In the prior art, an air pump specially designed for this purpose is required in the device for this purpose, which, however, is very rarely actually used. If a peristaltic pump is used specifically for infusion as the active conveyor device 36 in accordance with the invention, this pump can also be used for conveying gases instead of infusion liquid. This not only results in a simpler device design by dispensing with the special air pumping device but also has advantages in terms of hygiene and sterility, as the interchangeable cassette 1 is sterilized and is also regularly replaced. As an optional accessory, a preferably sterile and/or single-use bacteria filter can, for example, be attached to the bottle connection of interchangeable cassette 1, which filters the infusion air sucked in in this case.

[0072] FIG. 2 shows another exemplary embodiment of a cassette 1 according to the invention in a block diagram. The features functionally identical or equivalent to FIG. 1 are provided with the same reference numerals and reference is made to their description above.

[0073] The main differences between this embodiment according to the invention and FIG. 1 are, according to the invention, that in the infusion area only one active infusion is carried out by means of a conveyor device 36. The infusion valve 35 is here only optionally designed as an additional shut-off against the patient—but can also be omitted, especially if the liquid conveyor device 36 already has a sealing effect. The infusion path additionally shows an optional passive or active ripple compensation element 59 for a peristaltic pump 36, which is not absolutely necessary according to the invention. A passive compensation can, for example, be formed with a flexible area of the liquid channel which has the effect of a balancing bellows which cushions the pressure or flow rate ripple by deforming according to the ripple. Alternatively or additionally, active ripple compensation can be applied, in which an actuator on the device side deforms a flexible area of an infusion liquid channel and thereby compensates for pressure or flow rate ripple effects. The actuator can be controlled, for example, on the basis of values from the pressure sensor 37 and/or information about the rotary position of the peristaltic pump 36. According to the invention, a dynamic variation of the rotational speed of the peristaltic pump can also take place in such a way that the ripple effect of the conveyor device is minimized. In contrast to a normal, uniform rotational movement (with an optionally accelerated or decelerated phase in the case of changes in flow rate) as applied in the prior art, no strictly uniform rotational movement of the roller head takes place during conveying, but the rotational speed is modulated with the period duration of the roller interventions in such a way that the flow rate ripples occurring with this period duration are compensated as far as possible. Thus, a temporary acceleration or deceleration of the roller head movement occurs when a roller enters the area of the inlet or outlet of the squeezing channel (inlet or outlet, depending on which side of the ripple is to be compensated, i.e. when feeding or suctioning).

[0074] In the aspiration area, the waste bag 56 can be attached directly to cassette 1 in accordance with the invention. In addition to the aspiration connection 50a, a second, optional aspiration connection 50b with corresponding aspiration valves 51b and 50b is also shown for selection. In a Venturi system, the optional pressure sensor 10b can additionally monitor the pressure in the suction chamber of said system.

[0075] According to the invention, the infusion pressure can also be adjusted much more quickly than is possible with prior art technology. This can be done in particular depending on the surgical step or special circumstances that occur during the operation.

[0076] With the data known according to the invention which relate to the flow rate of the active infusion as well as the aspiration, the tightness of the incisions (=opening in the eye) can also be determined and this information can be made available for display or further processing.

[0077] The embodiments of an active infusion according to the invention described here offer a number of advantages over a known infusion system, such as a gravity infusion or an infusion by pumping air into the infusion surface. In particular, an active infusion according to the invention, especially with a peristaltic pump, offers advantages such as: [0078] Simplification of the setup of the operation and the commissioning of the device—and thus time saving, especially since an initial filling of the infusion system is designed significantly easier and faster. [0079] Reduced risk of sterility errors, especially when setting up the device. [0080] Faster pressure changes during the intervention than in the prior art can be carried out, which offers many application possibilities not known until then. [0081] Independence from a special supply of the infusion liquid, especially with regard to bottle size and bottle type, as this has no effect on the active infusion according to the invention. [0082] Additional monitoring functionalities, parameter evaluations, safety and comfort functions, etc. can be implemented. [0083] There is less waste because air filters, long needles for the infusion set, tubes, packaging etc. can be saved. Only the interchangeable cassette, which is required for aspiration anyway, is required, which can optionally be designed to be sterilizable several times. The costs of consumables will also be reduced.

[0084] FIG. 3a and FIG. 3b show a further embodiment of a cassette 1 according to the invention, each in a view from the right and left front. In the figures, the functional elements already described in the block diagram are shown and marked again. In this example, cassette 1 is shown as a basic cassette 1a, at least approximately cuboid in shape in its outer contours, with a projecting plate as the front section 1b. On the front section 1b there are connections for tube systems, in particular those to the surgical handpiece, to the infusion liquid reservoir 30, and to a waste bag 56. Preferably these connections 33,38,50,55 are mechanically and/or geometrically coded as shown in order to exclude the danger of incorrect connection and confusion.

[0085] In the example of an embodiment shown here, the functional elements of cassette 1 are divided between both of the shown outer shell halves 41 and 42 of cassette 1, thus enabling a compact structure to be achieved. The squeeze pump sections 36 and 52 are especially arranged on one cassette side 42, and the valves and pressure sensors are arranged on the opposite cassette side 41. Such a division of the functional elements is not mandatory, but can be advantageous with regard to gripping or clamping cassette 1 in device 99, in which clamping, fixing and/or fine positioning of cassette 1 in device 99 can take place simultaneously with pressing of the roller head(s) of the peristaltic pump. The movement required to clamp the cassette in the device 99 can only be carried out from one side, preferably from the side of the peristaltic rolls. The following figures illustrate in detail another exemplary design of a peristaltic pump according to the invention of a cassette 1 according to the invention.

[0086] FIG. 4 shows an exemplary embodiment of a cassette 1 according to the invention in its end position in a cassette slot of a device 99. Cassette 1 was inserted by pushing it into the cassette slot in insertion direction 91 and can be done manually or at least partially automated or motorized. A part of the cassette slot is shown as a section, but cassette 1 is shown in a non-sectional manner. In the illustrated position of cassette 1 in device 99, rollers can press against the squeezing areas of peristaltic pumps 36 and/or 52, essentially orthogonal to the shown side of cassette 1 in direction 27, so that cassette 1 can be positioned and fixed according to the invention in device 99 at the same time. In this inserted state, the sensors and actuators on the device side are in a position with respect to the cassette in which they can interact with their respective associated functional elements of cassette 1 for the intended purpose.

[0087] FIG. 5 schematically shows such a clamping and fixing of the inserted cassette 1 in the device 99 in a side elevation view, with viewing direction at the peristaltic pumps of cassette 1 (direction 27 in FIG. 4). A roller head 72 on the device side with rollers 73 is shown, which rollers 73 roll on the bulging squeezing area 94 of the outer shell 42, which is formed of elastic soft plastic 44. With this unrolling, the squeezing area 94 is pressed by the rollers 73 sealingly onto the core part 43 of cassette 1 and, with a rotation of the roller head 72 around the rotation center 75, a volume in the squeezing area 94 between the rollers 73 is conveyed. For the rotation of the roller heads 72, the device 99 has a respective infusion drive 76 for the infusion conveyor device 36 and an aspiration drive 77 for the aspiration conveyor device 52.

[0088] In FIG. 6a, cassette 1 is inserted in insertion direction 91, which in this figure runs orthogonally to the drawing plane, into device 99 up to its end position, but is not yet clamped. This concerns a sectional view of the right and left rotation centers 75a and 75b of the two separate peristaltic pumps 36 and 52 from FIG. 5. In the example shown, cassette 1 shown in the section is essentially made up of three parts, with a left outer shell 41, a right outer shell 42 and a core part 43. Preferably the outer shells 41 and 42 are designed to be snapable, compressible or squeezable against each other and/or against the core part 43, e.g. with a hook system, a press-fit system or similar, which in particular cannot be designed to be detachable again. In this case, the outer shells 41 and 42 can in particular be designed as two-component injection-molded parts consisting of a rigid hard plastic component and an elastic soft plastic component. The elastic soft plastic part is then clamped and squeezed and/or positively engaged with the core part 43 so that the liquid channels or pipes are formed and sealed within cassette 1. In the section shown, the elastic portion 44 forms beads along the liquid channels which, in the assembled state, engage in depression in the core part 43—thereby effecting a liquid seal, in particular by squeezing the soft plastic 44 and/or forming a meander seal with at least one step. Partial areas of the soft plastic part 44 are accessible from the outside when cassette 1 is assembled and form the functional elements. The hard plastic part of the two-component injection-molded outer shells 41 and 42 has corresponding cut-outs for this which provide access to the soft plastic 44. Optional sterilizability of the entire cassette, for example in the autocalve, etc., can also be taken into account when selecting the cassette materials if a reusable embodiment is desired.

[0089] In this example of an embodiment according to the invention, cassette 1 is clamped after insertion and the roller heads 72 of the peristaltic pump are pressed in direction 83. As shown, the clamping force of the rollers 73 and/or the position alignment 82 can be determined by means of springs.

[0090] The actuators which are not visible here and which act on the valves 35, 39, 51, 51a, 51b and/or 57 are also arranged in device 99 in accordance with the invention and are designed, for example, as electromagnetically or electromotively or pneumatically actuated plungers in the device which act mechanically on the valve formations of cassette 1. The pressure sensing device 10, especially its coupling element, is also coupled in the inserted state of cassette 1 with the force sensor 11 on the device side, which is not shown here. As also the membrane on the cassette side of the pressure sensor 37 and/or 37c is brought into a functional operative connection with a force or pressure sensor on the device side.

[0091] FIG. 6b shows cassette 1 in clamped state in device 99, in which all sensors and actuators of device 99 correspond with their counterparts of cassette 1 for interaction. In the example shown, this is done by clamping cassette 1 in device 99 by pressing roller heads 72 against cassette in direction 83. Thus the cassette 1 is pressed in the drawing level to the left on corresponding mechanical stops. The rollers 73 squeeze the squeezing channels 94—wherein in the upper pump (e.g. the infusion pump 36) there is a section through the roller 73 with a squeezed squeeze cross-section 94 and in the lower pump (e.g. the aspiration pump 52) there is a section next to a roller 73 and correspondingly an unsqueezed squeezing cross-section 94. With the centering elements 82, which in this example also form the rotation axis 75 of the roller head 72, fine positioning of cassette 1 in device 99 is also achieved when cassette 1 is clamped.

[0092] FIG. 7a shows an exemplary embodiment of a cassette 1 according to the invention in which a cassette-side pumping device 36 for the active infusion according to the invention and a further pumping device 52 are shown.

[0093] The illustration shows a first pumping device 36 for infusion and a second pumping device 52 for aspiration, separate from the first pumping device. These pumping devices are formed with the soft areas 44 of the outer shell 42, which form outwardly curved squeezing channels 94. As a result of the intervention of rollers 73, these squeezing channels 94 are pressed locally sealingly onto the core part 43. By moving the roller 73 along the squeezing channels 94 a volume can be conveyed in the squeezing channels 94. This movement can be achieved by rotating a roller head 72 around the rotation axis 75b, wherein the roller head 72 carries the rollers 73a and 73b. Especially shown are the rollers 73c and 73d on the device side, which move on concentric circular paths and engage in the respectively assigned squeezing channels 94c and 94d on the cassette side and form the pumping device 52 in cooperation with these. The same applies to the pumping device 36, wherein for the sake of clarity the rollers assigned to the squeezing channels 94a and 94b are not shown here.

[0094] A partial aspect that can be carried out according to the invention in this specially further developed embodiment for the reduction of ripple effects is the dual pump design with at least two adjacent squeezing areas 94c and 94d. These are designed and arranged in such a way that the ripple of the two adjacent squeezing channels 94c and 94d occurring due to the squeezing pumping effect is compensated as much as possible and thus the overall ripple of the pump is reduced. As shown, this can be achieved, for example, by mutually offset squeezing rollers 73c and 73d, which cause a phase shift of the pressure or flow rate ripple generated by the two squeezing channels 94c and 94d. The two inlets and the two outlets of the squeezing channels 94c and 94d are hydraulically connected to each other. In particular, a phase shift of the ripple curves by approx. 180 degrees for two channels can result in an advantageous reduction. With a different number of squeezing channels 94, the phase shift must be selected accordingly in a different manner. Alternatively or additionally, the position and/or shape of the inlets and/or outlets of the two squeezing areas 94 can be designed differently in order to effect said phase offset and/or a further ripple reduction. Thus, a ripple reduction can be achieved in relation to a single squeezing area according to such a further developed embodiment with a corresponding design.

[0095] In the case of an at least near concentric arrangement of two interconnected squeezing channels 94c and 94d which are shown here, it can also be considered that with their different arc radii also different arc lengths occur. For ripple compensation, the liquid channel cross-sectional dimensions, cross-sectional shapes and/or cross-sectional progressions of the outer arc 94c can therefore be designed in accordance with the invention so differently from the inner arc 94d that the volume conveyed per movement unit of the rollers 73 always remains at least approximately the same—or the volumes always balance each other out as far as possible and together result in the smallest possible ripple of the total volume conveyed, e.g. in such a way that over a complete revolution of the roller head carrying the rollers 73, the outer and the inner squeezing paths 94c and 94d convey at least approximately the same volume or have as far as possible a diametrically opposed volume ripple. Due to optionally different diameters of the engaging rollers 73c and 73d, different squeezing radii can also be taken into account in these considerations.

[0096] FIG. 7b shows the embodiment of FIG. 7a again in a sectional view through cassette 1. The liquid channels in the area of the peristaltic pump are formed in the interior of cassette 1 by the hard plastic core part 43, over which an elastomer part 44a of the outer shell 42 curved towards the exterior of cassette 1 forms a partial area of the liquid channel. This partial area, which is also referred to as squeezing area 94 of the pump, can be squeezed by engaging rollers 73 on the device side in the mode of action of a peristaltic pump so that the liquid or air in the liquid channel can be pumped when the roller 73 is moving. In particular, according to the invention, the cross-sectional area of the squeezing area 94 formed in this case can vary over its length. As shown in this example of an embodiment according to the invention, a taper of the cross-section towards the outlet of the pump and/or an enlargement or reduction of the (unsqueezed) cross-section at the inlet of the pump may be possible. In particular, an optimization of this change in cross-section can minimize pressure and/or flow rate fluctuations (also known as ripple) during conveying. An advantageous cross-sectional profile along the squeezing area 94 can also be determined, for example, by means of simulation and/or test series.

[0097] FIG. 8a shows cassette 1 with exemplary roller heads 72 in engagement. For the sake of clarity, only the lower rotatable roller head 72b, to which the rollers 73b are attached, is indicated in the figure—in the case of the upper pumping device, only the rollers 73a but not the associated roller head 72a are shown. In the example shown here, a first roller head 72a and a second roller head 72b of the respective separate infusion and aspiration pumps intervene on the same side of cassette 1. In another embodiment, the first and second roller heads 72a and 72b can also engage on opposite sides of cassette 1. In particular, but not necessarily, the rotary axes of the roller heads can be arranged opposite each other and form an at least approximately common rotary axis, which can bring advantages with regard to force distribution on cassette 1.

[0098] In this embodiment according to the invention, the squeezing areas are each only single, i.e. formed without a hydraulically parallel second squeezing channel as in the previous embodiment from FIGS. 7a and 7b.

[0099] In the example of the embodiment according to the invention shown here the two pumps 36 and 52 describe in each case at least approximately a semicircle on cassette 1. This results in an advantageous use of space on cassette 1 shown here by way of example, especially with simple handling and producibility. A concentric arrangement of the two pumps 36 and 52, which can also be implemented, would also be possible but would be comparatively more complex in terms of design. Alternatively, the beaded squeezing area 94 of the pump 36 and/or 52 can also be designed in a different embodiment with a different, in particular shorter arc length, wherein, however, an appropriate arrangement and number of rollers 73a or 73b must always be selected so that sufficient pumping behavior can be ensured, i.e. in particular in each squeezing area 94, at least one, preferably more than one, roller 73a is always engaged.

[0100] As illustrated in FIG. 8b, this can be achieved, for example, in accordance with the invention, by arranging the roller axes 74 at an angle to their unrolling planes on the squeezing channels 94, and preferably intersecting with this unrolling plane in the center of rotation 75 of the roller head 72 carrying the rollers 73. The frustoconical rollers 73 thus roll optimally onto the soft plastic area 44b of the outer shell 42, which forms the squeezing channels 94, and squeeze this against the core part 43. Alternatively, other geometries can also be used. The forming and arrangement are preferably carried out in such a way that the circumference of the roller 73a or 73b at one point is respectively proportional to the circumference of the circular path described by the roller at this point around the pivot 75a of the center of the roller head 72a.

[0101] FIG. 9 shows an exemplary embodiment of an example of an interdependent control according to the invention of the infusion conveyor device and aspiration conveyor device according to the invention. At the beginning the “normal state” is shown, where the infusion pressure P-inf is at least approximately constant and the aspiration volume V-asp is also at least approximately constant—e.g. an aspiration peristaltic pump rotates at an average constant speed. As a bar on the abscissa, which represents a time axis, an occlusion of the aspiration tool is shown, i.e. when a shattered lens particle clogs the tip of the suction needle, for example. This causes the aspiration negative pressure in the device to rise as shown on the corresponding curve. In accordance with the special partial aspect according to the invention described here, the infusion pressure can now be increased as a precaution in such a case with the rapid, dynamic controllability of the infusion pressure with the infusion conveyor device according to the invention from a certain aspiration vacuum, as shown in the corresponding curve. This can be carried out automatically by a control unit in device 99, i.e. without the intervention of a doctor. This occurs in preparation for the expected fracture of the occlusion, i.e. when the occlusion dissolves and the suction needle becomes free again—i.e. at the end of the occlusion bar shown. Then, due to the increased aspiration negative pressure, the aspirated liquid quantity is briefly increased—which could lead to an (at least slight) collapse of the eye. However, this can be compensated to a large extent by the partial aspect according to the invention of the precautionary, temporary increase in infusion pressure, since more infusion liquid has already been pumped during the occlusion detected (e.g. in the aspiration pressure increase) as a precaution in this case. Thus, when the occlusion is released, there is sufficient liquid in the eye so that collapse (=collapse of the anterior chamber) can be prevented or at least reduced. After loosening the occlusion and returning to the normal state of the aspiration negative pressure, the infusion pressure can also be normalized again.

[0102] FIG. 10 shows an exemplary embodiment of an example of a dynamic adjustment of the infusion pressure with which the active infusion according to the invention as the partial aspect according to the invention can be carried out. A diagram is shown in which, by way of example and simplified to the basic principle, the delivery volume F-asp of the aspiration conveyor device and the delivery volume F-inf of the active infusion conveyor device, which is controlled dependent thereon according to the invention, are shown. This dependency is illustrated here in an exemplary manner in such a way that the infusion is controlled as a function of a predetermined aspiration—in the sense of the invention, however, it is also possible to implement embodiments in which the desired infusion is predetermined and the aspiration is controlled as a function of this. In the diagram, the infusion quantity is always slightly larger than the aspiration quantity, since leakage losses are compensated when the eye is opened. The shown dependence on infusion and aspiration is preferably used as a kind of pilot control, which can additionally be superimposed by a regulation of the actual infusion pressure. The regulation is thus simplified and can be formed more dynamically, since the control deviation to be compensated is only small. In addition, with a significantly longer time constant, the pilot control can also be slowly adjusted according to the actual leakage loss if necessary and adapted to the actual losses occurring during the specific operation. For example, at the beginning of the intervention the pilot control can be carried out with a leakage rate compensation of 7%, for example, which is usual for this intervention according to experience, which percentage is then e.g. adjusted to 5%, if the superimposed regulation causes a continuous reduction of the infusion quantity over a longer period of time—the intervention opening is thus tighter than usually assumed.

[0103] In the upper part of the diagram, the infusion pressure P-sens at the pressure sensor in the cassette, corresponding to the infusion flow rates F-inf and adapted according to the invention, is also shown. The shown increase of the infusion pressure P-sens in the cassette, which is carried out according to this aspect of the invention depending on an increase of the flow rate F-inf, in particular an increased pressure drop in the line to the patient due to flow velocity is compensated for and results in a more balanced, more constant infusion pressure P-inf in the eye than in the prior art. Parameters for this flow rate-dependent target infusion pressure adjustment, e.g. the curve of the adjustment P-sens, can be determined, stored and provided experimentally or computationally for a tube set used in each case.

[0104] In the prior art, without active infusion, the above-mentioned advantageous further developments cannot even be taken into consideration, since such prior art systems reacting with inertia cannot be implemented. In addition, the problems which these advantageous further developments solve are not even known in the prior art or are of obvious relevance.

[0105] Another prior art problem is that relatively thin tubes are often used for the infusion, and therefore the pressure drop between the BSS bottle and the device cannot be neglected, especially with high infusion flow rates. It also happens frequently that a negative pressure forms in the BSS bottle, which has a negative effect on the infusion pressure in the prior art. A filter in the drip chamber, for example, which causes too much pressure drop, also has a negative effect. In these cases, gravity infusion results in less pressure in the eye and thus less stability.

[0106] With the active infusion according to the invention all this does not play a role, since the above problems do not, or at least hardly, affect the infusion pressure in the eye, or are actively compensated by the active infusion.

[0107] In particular, pressure measurement on the patient side of the liquid delivery device together with pressure regulation via a peristaltic pump can compensate for the pressure losses mentioned above. In addition, the peristaltic pump can also have a suction effect from the direction of the BSS bottle, which means that the flow rate can be compensated even with high pressure drops in the line, drip chamber, infusion bottle, etc. According to the invention—if necessary—higher flow rates from the BSS bottle can also be achieved than with just a gravity infusion, which can be very helpful in some surgical situations. In particular, it is possible to react quickly and dynamically to any changes, which makes the operation safer. In particular, according to the invention, such a fast and dynamic reaction to possible disturbances can be carried out automatically by the device, i.e. without or with only minor intervention by the personnel, especially via a controller module for the control of the infusion liquid delivery device, which automatically maintains or runs down predetermined target values and/or target value profiles of the infusion pressure on the basis of the sensor technology of the interchangeable cassette.

[0108] According to the invention, the infusion pressure measurement is thus arranged in the device, especially in the interchangeable cassette, especially in the flow direction of the infusion after the infusion conveyor device and before the infusion connection of the interchangeable cassette. In accordance with the invention, the control of the infusion—or the regulation of the infusion pressure at the remote surgical instrument connected via the line—is carried out exclusively via the control of a motor drive of the infusion conveyor device, which provides a volume conveying with a defined, known delivery volume. According to the invention, only one pressure sensor in the change cassette is required, since pressure drops are compensated via the line on the basis of the known delivery volume and the resulting flow rate or the flow velocity of the infusion medium through the line. Therefore, no special handpiece or surgical instrument is required for the infusion according to the invention, and in particular only a fluidic and no electrical connection. In addition, according to the invention, for example when an occlusion in the aspiration path is detected by an aspiration pressure sensor attached to the aspiration path, a pressure change in the infusion can occur which is especially dependent on the aspiration and which is especially also preventive. According to the invention, a leak rate compensation of the known infusion volume in comparison to a known aspiration volume can also be formed, for example by controlling the infusion conveyor device with a defined higher known delivery volume than that of an aspiration conveyor device and/or always providing a defined minimum delivery volume of the infusion.

[0109] In other words, one embodiment of the invention relates to a method with remote sensing pressure regulation at an infusion point connected to a conveyor device via a line, in which a pressure drop in the line is determined depending on a delivery volume of the infusion medium and a target value for a pressure of the infusion medium at the conveyor device is adjusted accordingly. In particular, this can be carried out, for example, by detecting a pressure of the infusion medium by means of a pressure sensor in the device arranged between the peristaltic pump and a connection to the line, and increasing a target value of the pressure as a function of the delivery volume to compensate for a pressure drop in the line, especially when these methods are provided in an ophthalmological device.

[0110] In other words, in an ophthalmological device an infusion pressure at the end of an infusion tube—i.e. the eye—can be determined according to the invention by knowing a pressure in the device and a flow volume for a known infusion tube. In comparison with pressure measurement directly on the eye for example, this is not only easier to install and less prone to errors but also results in an advantageous pressure regulation behavior for this specific application.