Artificial ocular implant comprising a specific intraocular pressure measuring device

Abstract

One aspect of the invention relates to an artificial ocular implant (1) comprising a carrier (4) and an intraocular pressure measuring device (8), wherein the intraocular pressure measuring device (8) is arranged on the carrier (4) and comprises a light source (10), a light receiver (11), and at least one photonic light guide (9, 9') and / or at least one perforated light guide (9, 9'), wherein the photonic and / or perforated light guide (9, 9') is designed to vary the guidance of light from the light source (10) depending on a deformation caused by the application of a force, wherein the light receiver (11) is coupled to the photonic and / or perforated light guide (9, 9') in order to receive light guided by the photonic and / or perforated light guide (9, 9').

Description

[0001] Artificial eye implant with specific eye pressure measuring device

[0002] Technical area

[0003] One aspect of the invention relates to an artificial eye implant. The eye implant comprises a carrier. Furthermore, the eye implant comprises an eye pressure measuring device.

[0004] State of the art

[0005] In conventional cataract surgery, the diseased natural lens is removed from the capsular bag through an incision in the cornea and replaced with an intraocular lens (IOL), which is inserted into the eye through the same incision and placed into the capsular bag. In recent decades, cataract surgery has evolved from an implant procedure for correcting clarity to a refractive procedure in which the implant corrects both clarity and refractive error. In addition to advances in optical design, patients can also benefit from additional, non-optical functions of intraocular lenses. Among other things, intraocular pressure is of interest, as elevated intraocular pressure is an important risk factor for glaucoma. Glaucoma is one of the most common chronic eye diseases in people over 40 and a leading cause of blindness worldwide.A large proportion of glaucoma cases remain undetected in the general population because the disease is silent and asymptomatic. Even when diagnosed, it can be difficult to determine whether the disease is progressing slowly or rapidly. Vision may only deteriorate in advanced stages of the disease, with irreversible damage to the optic nerve.

[0006] Therefore, early detection of elevated intraocular pressure is crucial to maximize the benefit of treatment for patients and prevent blindness. Elevated intraocular pressure can be either a complication in the early postoperative period after cataract surgery or a sign of an incipient or progressive disease, such as glaucoma.

[0007] It is known that intraocular pressure is measured during doctor's visits using a tonometer operated by medical personnel. These methods are usually limited to individual snapshots of intraocular pressure and also only provide indirect measurements of intraocular pressure.

[0008] An eye implant is known, for example, from WO 2013 / 185757 A1. There, it is provided that a membrane rests against a stationary and non-deformable photonic crystal. Depending on the pressure acting on the membrane, the contact surface on the photonic crystal is larger or smaller. The membrane is illuminated with a light source external to the implant and also external to the eye in order to visualize the area with which the membrane rests against the photonic crystal. An external measuring device determines the size of the area with which the membrane touches the photonic crystal. This can then be used indirectly to determine the pressure. However, this known overall system has significant disadvantages in that the patient is adversely affected by the external irradiation of the light onto the eye.Furthermore, with this system, eye pressure measurement can only be performed when the patient is in the doctor's office and this external light exposure is performed. Furthermore, such external light exposure is also prone to errors, meaning the measurement results may not be sufficiently accurate. A further disadvantage is that the generated signal must be transmitted through the ocular structures to an external source and may also be subject to interference from reflection, scattering, or absorption in the tissue.

[0009] Description of the invention

[0010] The object of the present invention is to create an artificial eye implant in which the measurement of eye pressure can be performed precisely and with both temporal and spatial variability. This object is achieved by an artificial eye implant according to the independent claims.

[0011] One aspect of the invention relates to an artificial eye implant. The eye implant has at least one carrier. The artificial eye implant further comprises an eye pressure measuring device. This eye pressure measuring device is thus particularly designed to measure eye pressure, in particular intraocular pressure, especially when the artificial eye implant is arranged in the eye. The artificial eye implant is therefore designed to measure eye pressure independently in the implanted state. This also makes such an eye pressure measurement possible in an automated manner.

[0012] The ocular pressure measuring device is arranged on the carrier. It is arranged completely and directly on the carrier. The ocular pressure measuring device has at least one light source arranged on the ocular implant itself, in particular the carrier. Furthermore, the ocular pressure measuring device has a light receiver. This light receiver is arranged on the ocular implant, in particular the carrier. The ocular pressure measuring device advantageously also has at least one light guide, such as in particular a photonic light guide. This at least one photonic light guide is designed to conduct light from the light source to the light receiver. In particular, this light conduction occurs depending on a deformation of the light guide caused by the application of a force. In particular, the light guide is deformable in a defined region that has the optical interference structure, here the photonic structure.This photonic structure itself is elastically deformable. This photonic light guide enables the light from the light source to be guided in a defined manner to the light receiver, with this light guide changing automatically depending on the force applied to the light guide. This force, which correlates with pressure on the light guide, is generated, for example, by the aqueous humor in an eye when the ocular implant is implanted. The light receiver is coupled to this photonic light guide to receive light guided by the photonic light guide.

[0013] An artificial eye implant has thus been created which has a complete eye pressure measuring device on the implant itself. The full functionality of eye pressure measurement is therefore enabled on the eye implant itself. It is therefore not necessary to shine light from outside the eye implant or from outside onto a patient's eye in order to perform an eye pressure measurement. It is precisely through the complete integration of an eye pressure measuring device in or on the eye implant that eye pressure measurement can be carried out in a more diverse and variable manner in terms of location and time, and can therefore also be performed without a visit to a medical professional. This also enables comprehensive, and in particular continuous, monitoring of eye pressure. The specific design of this eye pressure measuring device, as proposed above, also enables a more precise measurement of eye pressure.The light guide in particular has a dual function. On the one hand, it guides the light in a specific way, and on the other hand, its design as a photonic light guide makes it possible to precisely detect even small pressure changes due to the changing light conduction of the light guide. This also allows the eye pressure to be determined very accurately. The photonic structure of the light guide is an example of a fiber optic disturbance structure in the light guide, which, depending on a deformation of the structure, either specifically transmits the coupled-in light or not. The fiber optic disturbance structure can, in addition to or instead of, have other elements, such as holes, in order to specifically disrupt the light conduction depending on the deformation of this structure.

[0014] Photonic crystals, especially optical nanostructures, are capable of influencing photons through their structure, for example, by enabling the selective transmission or deflection of specific wavelengths. A photonic crystal generally consists of periodically repeating regions with high and low dielectric constants, which create so-called "photonic band gaps." This is generally achieved through destructive interference of the wavefunction of propagating photons of a wavelength that correlates with the periodicity of the photonic structure. Thus, a photonic crystal prevents light of a specific wavelength propagating within the structure from escaping in a defined and desired manner, thus fulfilling its intended purpose.

[0015] Due to the elastic design, the photonic structure changes depending on the deformation and influences the wavelengths of light that can propagate through the polymer from which the structure may be made. The deformation leads to a partial change in the photonic structure, which in turn leads to a shift in the wavelength of the photonic band gap. As a result, for example, white light propagating along a waveguide covered with such a polymer changes its properties with respect to certain wavelengths, leading to a signal drop for certain wavelengths at the receiving end of the light guide. Alternatively, the intensity of light of only a certain wavelength can decrease at the receiving end, in particular to the point where it is no longer received at all.

[0016] The signal received at the light receiver depends on the strength of the deformation of the photonic structure, with higher pressures leading to greater deformation and thus to a greater reduction of the signal.

[0017] This concept offers several advantages, as the sensitivity and detection range can be adjusted by the intensity of the propagating light, the length of the light guide, the elasticity of the photonic structure, and / or the properties of the photonic band gap. Therefore, this system can be highly adapted to detect pressure changes with specific ranges and sensitivities.

[0018] The eye implant also makes it possible to obtain precise measurements of actual intraocular pressure, regardless of corneal thickness and corneal deformation.

[0019] In one embodiment, the ocular pressure measuring device is arranged entirely on the carrier. This carrier is functionally designed accordingly and can accommodate the aforementioned components. This also enables a compact arrangement of the components of the ocular pressure measuring device on the ocular implant.

[0020] In one embodiment, the photonic light guide is at least one light-conducting, in particular tubular, hollow body. The light guide can therefore have just one hollow body or multiple hollow bodies. This light guide, in particular the hollow body, has at least one elastically deformable wall that delimits, in particular directly delimits, a cavity of this hollow body. If multiple hollow bodies are part of the light guide, for example, only one hollow body can have the elastic structure. The other hollow bodies can guide the light unhindered. This wall has, at least in some regions, a photonic crystal as a light-conducting interference structure, in particular on an inner side facing the cavity. Such a light guide generates a very specific structure that enables the particularly efficient guidance of light in the cavity from the light source to the light receiver.This also means that an emitted amount of light can generally be guided to the light receiver with very little loss thanks to this structure of the light guide. It is precisely this structure and in conjunction with at least one element that disrupts the light transmission in a defined way, here in particular at least this photonic crystal, that allows this change in light transmission to be carried out very precisely. This in turn also allows the change in this light transmission to be detected very quickly and precisely, even with the smallest forces and consequently the smallest pressure changes. This is because even small pressure changes lead to a change in light transmission due to this elastic wall with the specific optical transmission disruptive structure, namely at least the photonic crystal, which in turn can be detected very precisely by the light receiver.

[0021] In one embodiment, the photonic crystal is designed as a photonic nanostructure. This is particularly integrated into the wall. The wall of the light guide, which has this optical transmission interference structure and delimits the cavity, can also be referred to as a specifically designed membrane.

[0022] In one embodiment, the photonic crystal is integrated into the wall. It can thus be formed integrally with the wall. It is possible that this photonic nanostructure is created, for example, with a laser or through specific etching and / or surface treatments.

[0023] In one embodiment, the ocular pressure measuring device can be applied to the carrier using a process known as cold welding. This involves activating the surface of the ocular implant with a reactive plasma that generates reactive hydroxyl groups. If certain materials, such as polymers, metals, polymer-coated metals, or surface-modified metals, are selected for the pressure-sensitive areas, these can themselves contain hydroxyl groups. Under sufficient pressure, these groups can then fuse together, expelling water, and form strong covalent bonds. Using this "cold welding" technique, the components can be "glued" directly to the ocular implant after plasma treatment.Components that are sensitive to the surrounding water, for example because they are electrically conductive, could then be passivated with a layer of parylene, which is known to be biocompatible, non-conductive and chemically inert.

[0024] Another possibility involves modifying the surface of the ocular implant, especially the carrier, with other chemical groups after plasma treatment, for example, through the use of alkoxysilanes. By modifying the pressure sensor components with complementary groups that can react with the functionalities immobilized on the ocular implant, especially the carrier, adhesion of the sensor can be achieved in this way.

[0025] In another option, some or all of the pressure-sensitive components are incorporated directly into the carrier during raw material manufacturing. In one example, the at least one inductive antenna could be placed inside the ocular implant, specifically the carrier, which also contributes to the insulation of this part.

[0026] In another option, the pressure-sensitive components are not simply placed on the ocular implant, in particular the carrier, but are formed in predefined grooves on the surface of the ocular implant, in particular the carrier.

[0027] It is also possible that the eye implant is produced as a 3D print, i.e. using 3D printing technology, especially with all components.

[0028] In one embodiment, the wall is designed to be elastic to the application of forces that result in pressures such as those that can occur in an eye due to aqueous humor. In addition, or instead of this, the wall is designed to be elastic to changes in force that result in pressure changes such as those that can occur in an eye due to aqueous humor. This makes it possible to measure both absolute pressure values ​​and pressure change values ​​very precisely. In particular, it is possible for very small pressure changes, for example, down to 1 mmHg, to be measured with this specific eye pressure measuring device. This allows even very small pressure changes to be detected quickly and with high precision.

[0029] In one embodiment, the optical fiber with the at least one optical interference structure comprises an elongated tube, at one end of which the light source for coupling the light is arranged, and at the other end of which the light receiver is arranged. Such a series arrangement of the aforementioned components creates a compact arrangement. Furthermore, a coupling of the light from the light source into the optical fiber with as little loss as possible, in particular a loss-avoiding arrangement, is enabled, and a coupling of the guided light from the optical fiber into the light receiver with as little loss as possible, in particular a loss-avoiding arrangement, is also enabled.

[0030] In one embodiment, the eye implant, in particular on the carrier, has at least one antenna. This makes it possible for the eye pressure measuring device to also communicate wirelessly. In particular, the eye pressure measuring device can thereby wirelessly transmit and / or wirelessly receive signals. This also makes it possible for signals for activating the light source to emit light and / or signals for activating the light receiver to be wirelessly received by the eye implant. In addition to or instead of this, it is also possible for signals from the light receiver to be wirelessly transmitted from the artificial eye implant externally to the eye implant. This also allows significant advantages to be achieved.This makes it possible for the eye implant to communicate externally with the eye implant and / or externally with the patient, both in the implanted state and independently of time and location. Especially if a patient, for example, also carries a portable device external to the body that is designed to communicate with the eye implant, the patient can independently activate these components of the eye pressure measuring device and measure the eye pressure at any time. Furthermore, this makes it possible to transmit information from the eye pressure measuring device externally to the eye implant in a variety of ways and independently, for example to the communication device carried by the patient. Such a communication device can be designed purely for communication with the eye implant. However, it can also be a communication terminal. For example, it could then be a smartphone or a tablet.In this context, a software application can be installed on such a communication device. This allows communication with the eye pressure measuring device. It is also possible for this communication device to also conduct additional, particularly wireless, communication, for example, with a medical professional. This allows a patient to transmit information about the eye pressure measuring device's readings to an ophthalmologist's office or hospital, regardless of location and time. This also allows them to discuss or clarify their current medical situation with medical professionals at any time and very quickly, without having to be on site.

[0031] It is possible to arrange two antennas. One antenna can be configured for transmitting, the others for receiving. It is also possible to arrange for one antenna to be configured for transmitting and receiving and to be associated with the light source, and another antenna to be configured for transmitting and receiving and to be associated with the light receiver.

[0032] Alternatively, the inductive antenna is used only to receive the external signal for power generation, while a radio wave generator is used to transmit the signal from the eye pressure measuring device. This can be part of the eye pressure measuring device.

[0033] For example, when activated by an external inductive force, the light generator or light source sends a corresponding signal with a specific wavelength through the light guide. The wavelength is chosen, for example, to fit the band gap of the photonic and / or perforated structure. At normal intraocular pressure, the structure completely reflects the light. This propagates the signal to the light receiver without signal loss, and the light receiver sends a "maximum" signal via the inductive antenna to an external receiver. When the intraocular pressure increases, the photonic and / or perforated structure deforms depending on the magnitude of the pressure increase. As a result, the band gap partially collapses and cannot completely reflect the light propagating through the hollow light guide.Thus, only a reduced portion of the original light intensity reaches the light receiver and transmits a reduced signal to an external receiver. Since the deformation of the photonic and / or perforated structure correlates with the increase in intraocular pressure, the amount of light arriving at the end of the light guide can be reduced in a defined manner. Since the bending of the photonic and / or perforated structure correlates with the increase in intraocular pressure, the amount of light arriving at the end of the light guide and the signal sent to the external receiver also correlate with the intraocular pressure.

[0034] In one embodiment, the light guide is curved at least in some regions. In particular, it has a particularly continuous arc shape. In one embodiment, this arc shape is adapted at least in some regions to a curved edge of the carrier. Especially when the carrier is lens-shaped or disc-shaped, such a shape of the light guide can enable a very space-saving and also edge-side arrangement of the light guide. This allows a very space-saving arrangement of the eye pressure measuring device on the carrier. Especially when the carrier additionally has another functionality, for example, has a defined optical imaging property in some regions, the positioning of the eye pressure measuring device on the carrier can be such that this optical imaging property is not impaired or is not impaired in a disruptive manner.

[0035] In one embodiment, the ocular implant is designed solely for measuring intraocular pressure. In this case, no further functionality is assigned to the ocular implant.

[0036] However, it is particularly advantageous if the artificial eye implant, in addition to measuring eye pressure, has another, different function. In particular, this function can be one that positively supports a patient's eye. For example, the eye implant can then also be designed as a medication depot. It can then contain one or more specific medications that, when the eye implant is implanted in the eye, supply the eye with this medication for a specific period of time, thus positively affecting the eye's function.

[0037] In addition to or instead of this, the eye implant can also have a defined optical function. For example, in this context it can be designed as an intraocular lens. In such an embodiment, the carrier can be formed by an optical part of the intraocular lens and / or by a haptic of the intraocular lens. It is possible for the intraocular lens to have a disk-shaped or disc-shaped optical part, from which one or more haptic parts are arranged protruding. However, it is also possible for the intraocular lens to be designed without haptics. In this case, it only has the disk-shaped or disc-shaped optical part. In other embodiments, it is also possible for the disk-shaped or disc-shaped optical part to have a radially outer ring or a peripheral ring.In one embodiment, this ring may be without an optical function and thus have no optical imaging properties. In one embodiment, the eye pressure measuring device may then be formed or arranged with at least partial components, in particular entirely, on such a peripheral ring.

[0038] In one embodiment, the light guide can be a separate component and mechanically fastened to the carrier. For example, an adhesive connection can be formed here. It is also possible for the light guide to be arranged on the carrier through thermal action, for example by locally melting at least one of the two materials, so that a material-to-material connection can be created here, for example. In another embodiment, the light guide can also be integrated into the material of the carrier. For example, such an integrated design of a light guide can be created by processing the material of the carrier. Appropriate processing of the material can be carried out, for example, using a laser.

[0039] A further independent aspect of the invention relates to an artificial eye implant. The eye implant has at least one carrier. The artificial eye implant furthermore has an eye pressure measuring device. This eye pressure measuring device is thus particularly intended to measure eye pressure, in particular when the artificial eye implant is arranged in the eye. The artificial eye implant is therefore configured to independently measure the eye pressure in the implanted state. This also makes such an eye pressure measurement possible in an automated manner. The eye pressure measuring device is arranged on the carrier. It is arranged completely and directly on the carrier. The eye pressure measuring device has at least one light source, which is arranged on this eye implant itself, in particular the carrier. Furthermore, the eye pressure measuring device has a light receiver.This light receiver is arranged on the eye implant, in particular the carrier.

[0040] The eye pressure measuring device advantageously further comprises at least one optical fiber, such as in particular a perforated optical fiber. This at least one perforated optical fiber is designed to conduct light from the light source to the light receiver. In particular, this light conduction occurs depending on a deformation of the optical fiber caused by the application of a force. In particular, the optical fiber is deformable in at least one defined region which has the optical fiber disturbance structure, in this case the perforated structure. This perforated structure itself is therefore elastically deformable. This perforated optical fiber therefore makes it possible to conduct the light from the light source to the light receiver in a defined manner, whereby this light conduction changes automatically depending on the application of a force to the optical fiber.This force, which correlates with pressure on the light guide, is generated, for example, by the aqueous humor in an eye when the ocular implant is implanted. The light receiver is coupled to this perforated light guide to receive light guided by the perforated light guide.

[0041] In such an artificial eye implant, it is also possible for this perforated light guide to be integrally formed in an elastic wall that defines a hollow light guide. In this embodiment, too, a force external to the light guide, for example, from the aqueous humor of the eye, can deform this wall with the holes, which in turn changes the light conduction. This is because light can then also be deflected through these holes or exit the light guide. Such a structure for a perforated light guide is very simple.

[0042] The holes are designed as non-through holes. They are specifically dummy holes. They can therefore also be referred to as hole troughs or depressions. In particular, the holes form a specific hole pattern that allows for this optical disturbance in a defined manner when the structure or the perforated area is deformed.

[0043] This concept also offers several advantages, as the sensitivity and detection range can be adjusted by the intensity of the propagating light, the length of the light guide, the elasticity of the perforated structure, and / or the arrangement of the holes (number and / or relative position, and / or hole geometry). Therefore, this system can also be easily adapted to detect pressure changes with specific ranges and sensitivities.

[0044] In particular, the region of the optical fiber that has the optical interference structure, i.e., the photonic structure and / or the perforated structure, is generally significantly more elastic than the remaining region of the optical fiber, especially other walls that delimit a cavity of the optical fiber. In particular, this remaining region of the optical fiber is stiff compared to the region of the optical fiber with the optical interference structure.

[0045] Generally speaking, the artificial eye implant according to the invention combines the optical properties of elastic photonic crystals and / or perforated structures with the sensor capabilities of an optofluidic system, in particular with the associated signal transmission technologies. This enables more sensitive and precise sensor technology than previous concepts and opens up more possibilities for monitoring intraocular pressure. It also makes it possible to check the current intraocular pressure on demand using an external reader or to continuously monitor intraocular pressure using a wearable accessory. Patients are therefore able to check their intraocular pressure, for example, alone at home, independently of medical personnel.

[0046] Preferably, the optical disturbance structure, especially the elastic wall, is made of an elastomeric material, such as polydimethylsiloxane (PDMS). However, PDMS is not the only material. Many other materials that provide these properties are possible. The system is highly adaptable with regard to sensitivity to intraocular pressure. If the light guide is longer, small changes in intraocular pressure lead to gradually increased light losses. This can be further fine-tuned by adjusting the light intensity of the light source.

[0047] In addition, a target intraocular pressure can be defined via the pressure within the light guide, with the "zero point" of the maximum signal adjustable as needed. The pressure referenced for the change in the photonic structure and / or the perforated structure is optimized to a specific threshold, for example, 22 mmHg. Normal intraocular pressure is in the range of 10-

[0048] 21 mmHg, with an average of approximately 15 or 16 mmHg (±3.5 mmHg during a 24-hour cycle). An intraocular pressure of more than 21 mmHg is considered higher than normal. Therefore, the photonic structure and / or the perforated structure with a defined band gap for a specific wavelength and angle of incidence is used for an intraocular pressure below the threshold of, for example,

[0049] 22 mmHg.

[0050] In one embodiment, the external communication device can be a portable device for temporary measurements. For example, as long as the communication device is not in the vicinity of the ocular implant, the ocular pressure measuring device is inactive due to the lack of an inductive power source. To read the ocular pressure, the communication device is activated and brought outside the body near the implanted ocular implant. This allows the inductive signal to reach the ocular pressure measuring device, activate it, and send a signal to the communication device.

[0051] In an alternative embodiment, the communication device has an internal power source, a data memory, and the appropriate processing power to control the system. The communication device can be placed, particularly semi-permanently, near the ocular implant. This could be achieved by attaching the communication device to a wearable accessory, for example, to glasses worn by the patient, a headset, or the like. In another embodiment, the communication device could also be applied to the patient's skin or implanted subcutaneously. This would also allow the intraocular pressure to be measured continuously, for example, by activating the integrated sensor at short time intervals. This would also enable the intraocular pressure to be measured more consistently without the need for an external operator to handle the communication device.This would, for example, allow intraocular pressure to be measured overnight while the patient is sleeping or to create more coherent long-term intraocular pressure profiles.

[0052] In general, there are also other advantages to a proposed eye implant, namely no impairment of the patient's vision during the measurement, the possibility of performing the readout without pupil dilation, allowing a high degree of flexibility in positioning the patient's head in relation to the communication device and a lower susceptibility of the measurement to patient movements.

[0053] Furthermore, the generated light is transmitted only within the light guide, and no biological tissue can interfere with the signal transmission. The functionality of the proposed ocular implant and the readout of measurements are independent of the optical quality of the ocular implant and of tissue changes, such as those that might occur due to opacification of the anterior capsular bag wall.

[0054] The invention allows for a more continuous measurement if necessary, without restricting the patient's view or, in some cases, requiring his or her direct participation.

[0055] Furthermore, no attenuation of the structural change properties of the optical interference structure occurs even after a certain high number of switching cycles.

[0056] Material changes, such as calcification, of the eye implant are also avoided by integrated components.

[0057] Short description of the drawings

[0058] Embodiments of the invention are explained in more detail below with reference to schematic drawings. Figure 1a shows a schematic plan view of an embodiment of an artificial eye implant designed as an intraocular lens;

[0059] Fig. 1b is a schematic plan view of another embodiment of an artificial eye implant designed as an intraocular lens;

[0060] Fig. 2 is a perspective view of an embodiment of a light guide with a light guide interference structure of an eye pressure measuring device;

[0061] Fig. 3 shows a system with an artificial eye implant according to an embodiment of the invention and a communication unit external thereto;

[0062] Fig. 4 is a representation according to Fig. 3, wherein in Fig. 4 the communication unit is positioned differently than in the embodiment in Fig. 3.

[0063] Preferred embodiments of the invention

[0064] In the figures, identical or functionally identical elements are provided with the same reference symbols.

[0065] Fig. 1 shows a schematic plan view of an embodiment of an artificial eye implant 1. The artificial eye implant 1 here is an intraocular lens 2. The intraocular lens 2 has an optical part 3. This optical part 3 is an embodiment of a carrier 4. The optical part 3 is disk-like or disc-like in this case. In this embodiment, the intraocular lens 2 also has a haptic 5. In the example here, this is formed by two haptic brackets 6 and 7 protruding from the edge of the optical part 3. The design of the haptic 5 is not to be understood as exhaustive or restrictive here and in general. The haptic 5 can also be designed in a variety of other ways.

[0066] The intraocular lens 2 has an eye pressure measuring device 8. The eye pressure measuring device 8 is arranged entirely on the intraocular lens 2. In this exemplary embodiment, it is arranged entirely on the optical part 3. The eye pressure measuring device 8 here has a light guide 9. The light guide 9 has a light-conducting disturbance structure. This is defined and designed in such a way that the conduction of light through the light guide 9 can be disturbed in a defined manner depending on a defined deformation of the light-conducting disturbance structure. The light guide 9 is a photonic light guide here. However, in another exemplary embodiment, it can also be a perforated light guide. The photonic light guide 9 is designed here as an elongated body. The eye pressure measuring device 8 also has a light source 10. It further has a light receiver 11. As shown in Fig.As can be seen in Figure 1a, the light source 10 is arranged at one end of the light guide 9, in particular directly adjacent thereto. The light receiver 11 is arranged at the opposite end of the light guide 9, in particular directly adjacent thereto, in the exemplary embodiment. In the exemplary embodiment, the light guide 9 is curved. It is adapted, at least in some areas, to the curvature of an edge 3a of the optical part 3.

[0067] As can also be seen in Fig. 1a, the eye pressure measuring device 8 is arranged as close as possible to this edge 3a and is thus formed significantly off-center in the optical part 3. This does not impair the optical imaging properties of the optical part 3.

[0068] In the exemplary embodiment, the optical part 3 is provided with an optical imaging property over its entire geometry. It is also possible for the intraocular lens 2 to have a peripheral ring. The peripheral ring is arranged on the optical part 3 and represents a radially outer ring that circumferentially encompasses the optically effective region of the optical part 3. This peripheral ring preferably has no optical imaging property. In one exemplary embodiment, it can then also serve as a carrier, here in particular as a carrier ring, on which the eye pressure measuring device 8 is arranged, in particular completely. In such an exemplary embodiment, the haptic brackets 6 and 7, shown here for example, adjoin the peripheral ring on the outside.

[0069] In one embodiment, the intraocular lens 2 also has at least one antenna 12. The eye pressure measuring device 8 is thus configured to wirelessly transmit and / or wirelessly receive signals. In particular, signals for activating the light source 10 and / or for activating the light receiver 11 can be received in this context. It is also possible for this at least one antenna 12 to transmit signals from the light receiver 11 externally to the intraocular lens 3. Multiple antennas, for example, two antennas, are also possible.

[0070] In one exemplary embodiment, it can also be provided that the eye pressure measuring device 8, with at least partial components, is also arranged in the haptic element 5, if one is present. The eye pressure measuring device 8 can also be arranged entirely in a haptic element 5, in particular in a haptic bracket 6 and / or 7. In addition to or instead of this, the preferably present antenna 12 can also be installed at least partially in the haptic element 5.

[0071] Fig. 1b shows a further embodiment of an artificial eye implant 1. In this embodiment, too, the eye implant 1 is an intraocular lens 2. In contrast to Fig. 1a, the intraocular lens 2 is formed only with an optical part 3. It does not have a haptic element 5. In the embodiment in Fig. 1b, it is therefore possible for the diameter of the optical part 3 to be larger than in the embodiment in Fig. 1a. The embodiment in Fig. 1b can also provide for a peripheral ring, as explained above.

[0072] In another embodiment, the artificial eye implant 1 may not be designed to optically improve the eye's vision and thus may not be an intraocular lens 2. A wearer of such an artificial eye implant 1 is then, in particular, completely without defined optical imaging properties.

[0073] Fig. 2 shows an embodiment of a light guide 9, such as can be a component of the eye pressure measuring device 8. Here, it can be a photonic light guide. It is designed to guide light from the light source 10. In particular, this occurs as a function of a force applied by the light guide 9. The light guide 9 is furthermore configured to change this light guidance in a defined manner as a function of a deformation caused by a force applied, in particular only of a specific region of the light guide 9. This region is an elastic light guidance disturbance structure. The light guide 9 is here a light-guiding hollow body 13. The hollow body 13 is here particularly tubular in design. It has a cavity 14. In cross section, this hollow body 13 is designed with an angular contour in this embodiment. It can also be designed with a corner-free contour.In the exemplary embodiment shown here, the light guide 9 has a wall 15. This wall 15 is elastic. This elastic wall 15 has, at least in some regions, at least one optical transmission interference structure 16. In one exemplary embodiment, the optical transmission interference structure 16 is designed, in particular, as a photonic crystal 17, in particular as a photonic nanostructure.

[0074] It is also possible for this light conduction disturbance structure 16 of a light guide 9 to be formed, for example, by holes in the wall 15. In particular, further walls 18, 19 and 20, which also delimit a cavity 21 of the hollow body 13, are stiffer than the wall 15. In particular, the further walls, here the walls 18, 19 and 20, are dimensionally rigid or essentially dimensionally rigid with respect to forces such as can occur through the aqueous humor in an eye. In comparison, the wall 15, in particular the region having the light conduction disturbance structure 16, is elastic with respect to forces that result in pressures such as can occur through aqueous humor in an eye and / or is elastic with respect to changes in the effect of forces that result in pressure changes such as can occur through aqueous humor in an eye.

[0075] The arrows P1 and P2 symbolize, on the one hand, the coupling of the light into the light guide 9 from the light source 10, and, on the other hand, the coupling of the light from the light guide 9 into the light receiver 11.

[0076] Fig. 2 also shows an embodiment in which a light guide 9' is symbolically represented. This light guide 9' can be a perforated light guide. The at least one optical interference structure 16 is thus a perforated area 17' in this case. This perforated area 17' is formed in the elastic wall 15. Otherwise, the light guide 9' is preferably designed according to the explanations of the light guide 9.

[0077] Also possible is an optical fiber having the photonic crystal 17 and the perforated region 17' in at least one elastic wall 15. A system 22 is shown in Fig. 3. The system 22 comprises an artificial eye implant 1. This can be an intraocular lens 2, as explained above. This artificial eye implant 1 can communicate wirelessly with an implant-external communication unit 23 or a communication device by means of the at least one antenna 12. This external communication unit 23 can also be arranged externally to an eye 24 in which the artificial eye implant 1 can be implanted. It can also be arranged externally to a person 25. In particular, it can also be arranged at a distance therefrom. It is also possible for this communication unit 23 to be arranged remotely from the patient or person 25.For example, it can be several meters or even significantly further away from the person 25. With at least one antenna 23a, the communication unit 23 can wirelessly exchange signals with the antenna 12. With a receiver 23b, this communication unit 23 can receive signals from the eye implant 1. This makes it possible to transmit control signals and / or data signals and / or energy signals from the communication unit 23 to the eye implant 1. On the other hand, data signals can be transmitted from the eye implant 1 to the communication unit 23.

[0078] Fig. 4 shows a symbolic and schematic representation of an embodiment of a system 22 in which, in contrast to Fig. 3, the communication unit 23 is carried by the person 25. For example, the communication unit 23 can then also be worn on the body of the person 25, in particular arranged directly thereon. In particular, an arrangement of this communication unit 23 can thus also be provided, for example, in contact with the skin.

Claims

Patent claims 1. Artificial eye implant (1) with a carrier (4) and with an eye pressure measuring device (8), characterized in that the eye pressure measuring device (8) is arranged on the carrier (4) and a light source (10) has a light receiver (11) and at least one photonic light guide (9), wherein the photonic light guide (9) is designed to change a conduction of light from the light source (10) depending on a deformation generated by a force, wherein the light receiver (11) is coupled to the photonic light guide (9) in order to receive light guided by the photonic light guide (9).

2. Artificial eye implant (1) according to claim 1, characterized in that the eye pressure measuring device (8) is arranged entirely on the carrier (4).

3. Artificial eye implant (1) according to claim 1 or 2, characterized in that the photonic light guide (9) is at least one light-guiding, in particular tubular, hollow body (13) which has at least one elastically deformable wall (15) which delimits a cavity (19) of the hollow body (13), wherein the wall (15) has, at least in regions, a photonic crystal (17), in particular as a photonic nanostructure, on an inner side facing the cavity (19).

4. Artificial eye implant (1) according to claim 3, characterized in that the photonic crystal (17) is integrated into the wall (15).

5. Artificial eye implant (1) according to claim 3 or 4, characterized in that the wall (15) is elastic to force effects which cause pressures such as can occur due to aqueous humor in an eye (24), and / or the wall (15) is elastic to force changes which result in pressure changes such as can occur due to aqueous humor in an eye (24).

6. Artificial eye implant (1) according to one of the preceding claims, characterized in that the photonic light guide (9) is an elongated tube, at one end of which the light source (10) for coupling in the light is arranged, and at the other end of which the light receiver (11) is arranged.

7. Artificial eye implant (1) according to one of the preceding claims, characterized in that at least one antenna (12) is arranged on the carrier (4), so that the eye pressure measuring device (8) can wirelessly transmit signals and / or wirelessly receive signals, in particular can receive signals for activating the light source (10) to emit light and / or for activating the light receiver (11) and / or can transmit signals from the light receiver (11).

8. Artificial eye implant (1) according to one of the preceding claims, characterized in that the photonic light guide (9) is curved, in particular adapted to an arcuate shape of a curved edge (3a) of the carrier (4).

9. Artificial eye implant (1) according to one of the preceding claims, characterized in that the eye implant (1) is an intraocular lens (2) and the carrier (4) is formed by an optical part (3) and / or a haptic (5) of the intraocular lens (2).

10. Artificial eye implant (1) according to one of the preceding claims, characterized in that the photonic light guide (9) is a separate component and is mechanically attached to the carrier (4), or the photonic light guide (9) is embedded in the material of the carrier (4) is integrated, in particular is produced by processing the material of the carrier (4).

11. Artificial eye implant (1) with a carrier (4) and with an eye pressure measuring device (8), characterized in that the eye pressure measuring device (8) is arranged on the carrier (4) and has a light source (10), a light receiver (11) and at least one perforated light guide (9'), wherein the perforated light guide (9') is designed with at least one perforated region (17') to change a conduction of light from the light source (10) depending on a deformation generated by a force, wherein the light receiver (11) is coupled to the perforated light guide (9') in order to receive light guided by the perforated light guide (9').

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