GB2342718A

GB2342718A - Method for analysis and/or therapy of an eye

Info

Publication number: GB2342718A
Application number: GB9923990A
Authority: GB
Inventors: Peter Alfred Payne; Richard James Dewhurst; Emanuel Saul Rosen; Andrew Fink; Ali Sadr
Original assignee: Individual
Current assignee: Individual
Priority date: 1998-10-13
Filing date: 1999-10-12
Publication date: 2000-04-19
Anticipated expiration: 2019-10-12
Also published as: GB9822270D0; GB9923990D0; GB2342718B

Abstract

The method comprises the step of directing a laser radiation into the eye, the characteristics of the laser radiation being suitable to generate ultrasound at desired locations within the eye. In order to analyse the eye, the generated ultrasound is detected by a piezoelectric transducer. The generated ultrasound may also be detected during therapy of the eye by the laser in order to monitor the course of treatment.

Description

Ophthalmic Methods This invention relates to ophthalmic uses of lasers, in particular the methods for analysis and therapy of the eye utilising laser induced ultrasound.

There is considerable interest in medical applications of ultrasound and photo acoustic waves, sometimes known as laser-generated ultrasonic waves. This is because, in contrast to interrogating techniques such as X-ray imaging and scintigraphy, ultrasound offers the possibility of interrogating a subject with no harmful side effects.

Ultrasound imaging of cardiac structures, the vascular systems, the foetus and uterus, abdominal organs such as the liver, kidneys and gall bladder is known. Conventional ultrasound measurements of the eye, using piezoelectric devices to generate ultrasound, are known.

The present invention provides an improved method for analysing an eye using laser radiation to generate ultrasound at desired locations in the eye.

According to the invention there is provided a method for analysis and/or therapy of an eye comprising the step of directing laser radiation into the eye, the characteristics of the laser radiation being suitable to generate ultrasound at desired locations within the eye.

It is possible to generate ultrasound in this way at numerous locations within the eye using a single source. In particular, ultrasound may be generated at the back of the eye, at the sclera, choroid, retina or vitreous humour, or at the front of the eye, i. e. the cornea, lens, iris and ciliary body and the aqueous humour, by a single laser pulse. To reflect ultrasound from the retina requires the use of much lower frequency ultrasound signals than needed to make high resolution dimensional measurements of the front portion of the eye. Conventionally, this necessitates the use of two piezoelectric transducers.

The generated ultrasound may be detected by ultrasonic transducer means connected to the eye by an acoustic coupling medium. The method may comprise an analysis of the eye in which the time taken for the generated ultrasound to propagate from the location at which it is generated to the ultrasonic transducer means, or a time value closely related thereto, is measured, and information concerning the eye is derived therefrom. The information concerning the eye may comprise the spatial dimensions of the eye or of one or more components of the eye. The information concerning the eye may also comprise opacity measurements within the eye.

The laser radiation may be directed to the eye substantially along an axis which is substantially parallel to the optical axis of the lens. The term"substantially along an axis"is intended to encompass instances where a laser beam does not propagate along a single axis due to divergence of the beam or focusing of the beam, but, nonetheless, an"average"beam path is described by a single axis.

Alternatively, the laser radiation may be directed into the eye substantially along an axis which is substantially non-parallel to the optical axis of the lens. This enables inter alia"offaxis"White-White measurements to determine the dimensions of the ciliary sulcus.

The point of entry of the laser radiation into the eye may be varied. In this way, an image of the eye, or one or more components of the eye, may be constructed from measurements made at a plurality of points of entry of the laser radiation into the eye. In this way, a B-scan may be performed. The variation of point of entry of the laser radiation-which is preferably accomplished by traversing a laser beam vertically or horizontally across the eye-may be combined with"off-axis"measurements of the type described above.

Information concerning the lens may be derived from the generated ultrasound, such as the size and position of the lens.

Information concerning light scattering sources present in the eye may be derived from the generated ultrasound.

The opacity of the lens may be measured.

The presence of flare and cells and like scattering sources in the vitreous humour and/or aqueous humour may be detected.

Preferably, a device having ultrasonic transducer means and a source for directing the laser radiation to the eye combined in a single housing is used. Such devices are known from, or may be adapted from devices known from, British Patent Application GB 2 212 920 A and International Publication WO 94/28804.

The acoustic coupling medium may comprise a saline solution or a gel.

The invention provides a method for treating pathological lesions of the layers of the wall of the eye in which tissue destruction is effected by the laser radiation.

In this way, glaucoma may be treated by effecting destruction of the ciliary body.

Methods in accordance with the invention will now be described with reference to the accompanying drawings, in which: Figure 1 is a schematic diagram of apparatus for analysing an eye; Figure 2 shows the laser ultrasound sensor with housing; Figure 3 is a cross sectional side view of the head of the probe; Figure 4 is a first cross sectional side view of a human eye; Figure 5 a) and b) shows ultrasonic transducer response on two different time scales; and Figure 6 is a second cross sectional side view of a human eye showing the white to white dimension.

The invention comprises a method for analysis and/or therapy of an eye comprising the step of directing laser radiation into the eye, the characteristics of the laser radiation being suitable to generate ultrasound at desired locations within the eye.

Figure 1 shows apparatus for performing the method, comprising a pulsed laser 10 producing a beam of laser radiation-12 which is focused by a lens 14 into an optical connector 15 which is connected to an optical fibre 18. The laser beam 12 ultimately emerges from a source 20 which is one end of the optical fibre 18, this laser radiation then being directed into an eye 22 which is positioned in an acoustic coupling medium 24 such as a saline solution.

As shown in Figure 2, the source end 20 of the optical fibre 18 is mounted coaxially with ultrasonic transducer means 26 in a single housing 28.

Data are collected using a digital oscilloscope 30 (Tektronik TDS620A).

The oscilloscope 30 is triggered by the output of a photodiode 32 (type BPX-65) which receives a small proportion of the laser radiation from a beam splitter 34. The output of the ultrasonic transducer means 26 is inputted to the oscilloscope 30 at socket 36. Data are transferred to a computer 38 equipped with National Instruments Lab Windows (RTM) software for further processing and analysis. For observing small amplitude features more clearly, two cascaded low-noise wideband amplifiers (Comlinear type CLC 100) with a total gain of 40db (not shown) were used for amplifying the transducer output signal.

Figure 2 shows the portion of the apparatus comprising the optical fibre 18.

Laser radiation is focused into the optical fibre 18, which is of 600pm OD, via a connector. The optical fibre 18 passes through a signal manifold 39 which comprises a connection 39a for electrical connection to the transducer means 26. A cable 40 runs between the manifold 39 and the housing 28, the cable 40 containing the optical fibre 18 and electrical signal leads from the housing 28. Figure 3 shows the housing 28 in more detail. The housing 28 comprises a perspex shell, in which the ultrasonic transducer means 26 is located. Although the ultrasonic transducer means 26 might comprise a piezoelectric ceramic, it is preferred to use a piezoelectric polymeric material, preferably polyvinylidene fluoride (PVDF) or, most preferably, its copolymer with trifluoroethylene (TrFE). The PVDF is present on a film (Pennwalt Kynar film type 5028 NAD), the rear face of which is located on a conductive silver loaded epoxy support 42 (Circuit Works RTM, available from RS). The use of silver loaded epoxy is preferred because i) it exhibits advantageous mechanical properties of stiffness, acoustic impedance and good adhesion to PVDF and ii) it exhibits excellent electrical conductivity compared to conventional epoxy materials, resulting in increased detection sensitivity. A wire 44 makes electrical contact with the epoxy support 42, the main body of the wire 44 being located in cable 40. The housing 28 is coated with a silver loaded paint 46. The optical fibre 18 passes through the housing 28, preferably coaxially therewith.

Devices having ultrasonic transducer means and a source for directing laser radiation combined in a single housing are known from British Patent Application GB 2212920A and International Publication WO 94/28804. However, it should be noted that GB 2212920A is silent regarding the dimensions of such devices. Furthermore, WO 94/28804 is concerned with intravascular uses, and teaches that the outside diameter of the housing should be no greater than 3mm. There is no such contraint when making measurements of the eye using laser induced ultrasound, and, indeed, housings of larger dimensions are desirable since the size of the ultrasonic transducer means can be increased, leading to greater sensitivity. Devices used to perform the method of the present invention preferably comprise housings (as defined above) having an outside diameter (or corresponding dimension, such as width) of greater than 3mm, more preferably greater than 1 cm, most preferably greater than 2cm.

Figure 4 shows a cross section through a human eye. Substantially identical structural components are present in the eye of other mammalian species. The eye produces images by focusing light onto the retina 58 with the lens 54. The passage of light from the front of the eye to the back of the eye involves the traversal of the cornea 50, aqueous humour 52, lens 54, and the vitreous humour 56, the light then impinging upon the retina 58.

Ultrasound is generated by absorption of light at an interface between two media which have different coefficients of absorption. The generation and detection of ultrasound in a complicated structure such as an eye, which has numerous interfaces between different structural components, is a complex process controlled by numerous parameters. In particular, it has not previously been possible to generate and detect ultrasound in the vitreous humour or at the retina/vitreous humour interface. The latter is required if knowledge of the overall dimension of the eye along the optical axis of the lens is desired. It is necessary to generate penetrating, low frequency ultrasound. The intensity of the light reaching these regions of the eye should be high enough to generate detectable ultrasound, but not so high as to cause damage to the eye. This intensity is affected by the absorption and scattering properties of the various components of the eye.

Thus optical properties of the eye components at the wavelength of the laser radiation are important parameters. Pulse energy characteristics and the diameter of laser beam are also important parameters, since they determine the intensity of the laser radiation. It should be noted that if the laser radiation is not collimated, e. g., if it is focused, the spot size of the laser beam will vary at different locations within the eye. For non-invasive measurements, the incident laser intensity will generally be sufficient to generate ultrasound by thermoelastic expansion of the interrogated tissue. Experiments were performed using the frequency doubled output of a Nd : YAG laser 10 (Quanta-Ray GCR150) at 532mm. The laser 10 is Q switched, producing pulses of 10nec duration at a repetition rate of 1.25Hz with a pulse energy of 1.44mJ. The laser beam passes through a number of neutral density filters 48 in order to attenuate the laser radiation so as to achieve an appropriate laser intensity incident on the eye under investigation.

Absorption data for different eye components at 532nm is shown in Table 1. In Table 2 is shown amplitude reflection coefficients at interfaces between layers in the eye.

Amplitude reflection coefficients at the boundary between two consecutive layers are given by Z-Z z + Z2 R 1 2 where Z, and Z2are the acoustic impedances of the first and second layers respectively.

Absorption Ultrasound Acoustic Structural Percentage Coefficient(3) Density(4) Velocity(4) Impedance Component transmission (l) (cm-l) (Kg. m-3) (m. s-1) (Rayl) Comea 63% 3. 080 1076 1588 1708688 Aqueous humour 60% 0. 488 1003 1503 1507509 Lens 47% 0. 181 1071 1673 1791783 Vitreous humour 37% 0. 171 1009 1532 1545788 Retina 1%36. 106107115321640772 1-Percentage transmission through the eye reaching the anterior surface of a particular structure.

2-Estimated values.

3-These values were calculated using the Beer-Lambert Law.

4-Average values are used.

Table 1-Some optical and acoustic properties of bovine eyeballs

Type of interface Amplitude reflection coefficient Cornea/Aqueous humour 6. 26% Aqueous humour/Lens-8.62% Lens/Vitreous humour 7. 37% VitreousVitreoushumour/Retina-2.98% Table 2-Amplitude reflection coefficients at the boundary between layers of bovine eyeball It will be apparent to the skilled reader that other types of laser and other laser wavelengths may be utilised. Indeed, consideration of the parameters discussed above may suggest optimal wavelengths, spot sizes and pulse energies for the particular type of eye being examined.

Measurements were made using laser radiation from the Nd : YAG laser to probe fresh bovine eyes, which were positioned in the saline solution 24. Figure 5a and 5b show the time resolved output of the PVDF film 26. Waveforms A, B, C, D are obtained showing bipolar transients characteristic of ultrasound pressure waves.

Knowing the separation of the eye from the PVDF film 26 and the velocity of ultrasound through the various media, it is possible to calculate the depths of the interfaces producing waveform A, B, C, D. It is believed that waveform A corresponds to the saline solution/cornea interface. The other waveforms B, C, D correspond to depths of ca. 1. 70mm, 3.48mm and 30.60mm from the solution/cornea interface. These depths are expected if waveform B corresponds to the aqueous humour/cornea interface, C corresponds to the lens/aqueous humour interface and D corresponds to the retina/vitreous humour interface. These interfaces have been appropriately denoted A, B, C, D in Figure 4. Thus the depth 30.60mm associated with waveform D represents the overall dimension of the eye along the optical axis of the lens.

It should be noted that the waveform A may be attributable to more than one specific feature. Also there is no waveform readily attributable to the vitreous humour/lens interface, but this might be a sampling anomal. Table 1 shows that the absorption coefficients of the vitreous humour and the lens are very similar at 532mm, so difficulty in detecting associated ultrasound is perhaps not surprising. It is possible that there are larger differences in absorption properties of these components at different wavelengths, and thus this interface may be detectable using a different laser.

There are numerous possible extensions to the technique. For example, White-White measurements can be made by directing the laser radiation into the eye substantially along an axis which is substantially non-parallel to the optical axis of the lens. The optical axis of the lens is shown as a broken line in Figure 4. The white to white dimension is shown in Figure 6.

In another variation, the point of entry of the laser radiation into the eye may be varied. This might be accomplished by translating the source, i. e., by moving the housing 28. By doing this, a whole eye B scan can be performed. It is also possible to combine these two approaches, i. e., to traverse the point of entry of the laser radiation into the eye whilst making"off-axis"measurements, in order the provide additional information.

It may be possible to derive information concerning light scattering sources present in the eye from the generated ultrasound. Indeed, it is possible that some of the additional features present in the data shown in Figures 5a and 5b are caused by ultrasound generated at such scattering sources, although this has not been confirmed.

Alternatively, information may be obtained by comparing the intensities and/or shapes of the waveforms associated with the generation of ultrasound at specific interfaces.

Measurements of scattering sources might provide information on the opacity of the lens or the presence of flare and cells and like scattering sources in the vitreous humour and/or the aqueous humour.

It is also possible that the present method might be used for therapeutic purposes. In particular, it may be possible to use laser radiation to affect local tissue destruction, for example of the ciliary body as a treatment for glaucoma. The aim is to reduce the secretion of aqueous humour from the ciliary body and thus reduce the elevated intraocular pressure which is associated with advanced glaucoma. It is understood that tissue destruction would be achieved by local heating caused by the laser irradiation, and not by ultrasound, which will be generated as a by-product of the treatment. However, it is likely that detection of the generated ultrasound will be desirable so as to monitor the course of treatment. It is possible that higher laser intensities, causing ultrasound emission in the ablation regime, might be utilised. Alternatively, it is possible to utilise two separate lasers, possibly with laser radiation from both lasers propagating along the same optical axis. The first laser might operate at a relatively high laser intensity, for therapeutic purposes, causing the destruction of cells. Either simultaneously or sequentially, a second laser might be used for diagnostic purposes, monitoring the zone of therapy, or other zones within the eye. In a sequential scheme, the two lasers might operate at a common pulse repetition frequency, but with an appropriate delay between pulses from the two lasers. It is also possible for the two lasers to operate at different pulse repetition frequencies. A further possibility is to use a single laser, but to split the beam into a strong beam and a weak beam.

A technique currently used to treat glaucoma is to ablate the ciliary body from outside with a diode laser. This is placed a standard distance (about 1 mm) behind the edge of the cornea on the white of the eye and the laser radiation is applied for a few seconds. Because of anatomical variations, there is currently no way of determining if the laser radiation is correctly aligned with respect to the ciliary body, or of assessing how much damage has been done by the treatment. The method of the present invention might be very usefully combined with such prior art techniques to provide structural information and/or information on the alignment of the therapeutic laser beam. A two laser scheme would be employed. Information could be provided using ultrasound before, after or possibly even during the ablation.

The techniques described above with reference to glaucoma might be used to destroy other localised lesions of the inner aspect of the wall of the eye such as angiomas or certain malignant tumours.

In the present example the acoustic coupling medium is a saline solution.

Other media are within the scope of this invention, including gels, and indeed it is possible that such media might prove more comfortable to subjects undergoing examination using the present invention.

Claims

1. A method for analysis and/or therapy of an eye comprising the step of directing a laser radiation into the eye, the characteristics of the laser radiation being suitable to generate ultrasound at desired locations within the eye.

2. A method according to claim 1, in which ultrasound is generated at or in the vitreous humour or the retina.

3. A method according to claim 1 or 2, in which the generated ultrasound is detected by ultrasonic transducer means connected to the eye by an acoustic coupling medium.

4. A method for analysis of an eye according to claim 3, in which the time taken for the generated ultrasound to propagate from the location at which it is generated to the ultrasonic transducer means, or a time value closely related thereto, is measured, and information concerning the eye is derived therefrom.

5. A method according to claim 4, in which information concerning the eye comprises the spatial dimensions, of the eye or of one or more components of the eye.

6. A method according to any of claims 1-5, in which the laser radiation is directed into the eye substantially along an axis which is substantially parallel to the optical axis of the lens.

7. A method according to any of claims 1 to 5, in which the laser radiation is directed into the eye substantially along an axis which is substantially nonparallel to the optical axis of the lens.

8. A method according to any of the previous claims, in which the point of entry of the laser radiation into the eye is varied.

9. A method according to claim 8, in which an image of the eye or one or more components of the eye is constructed from measurements made at a plurality of points of entry of the laser radiation into the eye.

10. A method according to any of claims 6 to 8, in which information concerning the lens is derived from the generated ultrasound.

11. A method according to claims 1 to 8, in which information concerning light scattering sources present in the eye is derived from the generated ultrasound.

12. A method according to claim 11, in which the opacity of the lens is measured.

13. A method according to claim 11, in which the presence of flare and cells and like scattering sources in the vitreous humour and/or the aqueous humour is detected.

14. A method according to any of claims 3 to 13, in which a device having ultrasonic transducer means and a source for directing laser radiation to the eye combined in a single housing is used.

15. A method according to any of claims 3 to 14, in which the acoustic coupling medium comprises a saline solution.

16. A method according to any of claims 3 to 14, in which the acoustic coupling medium comprises a gel.

17. A method for treating pathological lesions of the layers of the wall of the eye according to claim 1, in which tissue destruction is effected by the laser radiation.

18. A method according to claim 17 for treating glaucoma in which destruction of the ciliary body is effected.