METHOD FOR MEASURING X-RAYS OR GAMMA RADIATION AND DEVICE FOR THIS

Abstract: According to the invention x-rays gamma radiation is measured by means of the Compton effect utilizing scattering towards a long and narrow filament of poly­ ethylene, lucite or another material having a low average atomic number. The radiation scattered from the filament (4) is measured by a detector (8) and the radiation to and from, respectively, the filament is shielded by collimators (2,3 , 6 and 7). The de­ tector (8) is connected to a multichannel analyzer which, in turn, is connected to a computer performing a re­ construction of the primary radiation from the measured spectrum. The measuring method is practical in use and very accurate.

Description: Clinical use of quantitative X-ray methods such as the determination of bone mineral content or tissue density for dose planning purposes demand a knowledge of the energy distribution of the x-rays. Spectrometry with germanium detectors requires counting rates of about 50000 pulses/second or less in order to avoid overlapping pulses (pile ups). With the high fluence from clinical x-ray tubes appropriate counting rates is attained only if the distance between the x-ray source and the detector is several meters and the collimators have diameters that are as small as 0.025-0.5 mm. This direct measuring method cannot be used in practice in clinical x-ray laboratories due to space limitations. Fig 2, the upper continuous line, shows a spectrum measured directly. Due to the practical difficulties of the direct measuring method it is only used to a small extent. Moreover, there will be problems with the alignment of the detector because it is easy to measure, by mistake, beside or on the edge of the x-ray focus which, of course, is not intended. An extremely efficient method for reduction of the pulse rate is utilizing Compton scattering i.e. the radiation is scattered of the electrons in a material. However, when the radiation is scattered in this way energy is lost to the electrons and as a result of this the original spectrum will be distorted, the consequence being, in turn, that this is no longer representative. Accordingly Compton scattering has not been utilized so far as a basis of commercial spectrometry. Fig 2, the lower curve solid, shows a Compton scattered spectrum. A method for using Compton scattering of x-rays is described in Medical Physics (1976) 3: 328-334 in an article by M. Yaffe, K.W. Taylor and H.E. Jones titled "Spectroscopy of diagnostics x-rays by a Compton scatter method". In this method Compton scattering against a foil is used. This method will only allow a poor reconstruction of the original spectrum. Consequently today no good technique seems to be available for the measuring of x-ray energy spectrums and the above mentioned method is a dead end since it does not provide the necessary preciseness Today therefore a precise method of measuring x-ray spectrums and a device therefor is lacking and the invention has as its object to provide a precise spectroscopic method and a corresponding device. In accordance with the invention this is astonishingly simple obtained by the method according to Claim 1 and the device according to Claim 2. In the invention, the above mentioned foil is substituted by a scatterer in the shape of a long and narrow filament or a long and narrow rod. Consequent calculations have shown that the major reason for the improvement is that the scattering angle is more exact and still provide the necessary mass and thus the necessary amount of electrons to provide the scattering. The results of the invention are further enhanced by using correct scattering algoritms, even taking into consideration that the incoming x-ray radiation is polyenergetic. By using a filament or rod a very well-defined scattering angle is obtained. Secondly, the scattering from the surrounding medium (air) is minimized as it is measured from the volume determined by the intersecting beam paths of the beam incident from the source and the beam path of the detector. Moreover, by using a very long and narrow filament or a very long and narrow rod having a circular cross-sectional area a possibility of varying direction is obtained as the scattering volume does not vary with the scattering angle. By using in a suitable further development of the invention a material for the rod or filament having a low average atomic number the Doppler effect is reduced which, in turn, brings a better reproduction of adjacent peaks in the spectrum. As suitable materials polyethylene, lucite or another material having a low average atomic number is suggested. The reconstruction of the primary spectrum from the measured spectrum is carried out by means of the following formulas which have recently been produced by the inventors. As the physics lying behind is complicated we will only give the final expressions. In the equation (E1) N hν (hν c )d(hν c ) is the number of photons registered by the detector between the energies hν c and hν c + d(hν c ) after correction for the distortion of the detector itself (detector response). N e = the total number of electrons in the scatterer r₀ = the standard electron radius = 2.82 * 10⁻¹⁵ m gives the radiation damping in the scatterer and in the air (attenuation). 1(a) = the distance in air between the scatterer and the detector. u a = the attenuation coefficient of air. u s = the attenuation coefficient of the scatterer. r = the radius of the circular and filamentous scatterer hν c = the energy of the Compton-scattered radiation hν₀ = the incoming energy resulting from the relation The scattering angle ϑ is found in the equations (E1) and (E3). The self energy of the electron = mc². In equation (E1) ΔΩ is the solid angle element subtend by the detector from a point in the scatterer on an average. In equation (E1)Φ 0,hν (hν₀) represents the approximately reconstructed radiation intensity (before scattering). This corresponds to Fig. 2, dotted line, except the peaks. We also reconstruct the peaks and must then work with a complicated expression containing numerical derivatives of Φ 0,hν (hν₀), equation (E1). The average kinetic energy T of the electrons in the scatterer is also included. The expression reads: Φ 1,hν in equation (E4) is only used for reconstruction on and around the peaks. Fig. 2, dotted curve, shows the total result when the equations (E1) and (E4) are combined. As is apparent, the reconstruction is very good. The difference between the continuous and dotted lines is very small. A practical illustrative example of the invention is apparent from the following description. Fig. 1 shows schematically a scattering chamber according to the invention and Fig. 2 shows the radiation curves already treated. The scattering chamber shown in Fig. 1 is substantially angular. In the first angle arm there is an aperture for incident, highly intensive x-radiation. Within the chamber there are a first collimator 2 and a second collimator 3 defining the radiation which thereafter hits the filament 4. The radiation passing the filament and past it passes out through an aperture 5 on the other side of the scattering chamber. At right angles to the direction of radiation through the collimators and the filament two collimators 6 and 7 are arranged and the radiation scattered in the filament passes through the collimators to a detector 8 in the other arm of the scattering chamber. In this case the detector is a High parity Ge-detector connected to a multichannel analyzer. This, in turn, is connected to a data processing unit reconstructing spectra according to the equations (E1)-(E4). a-c are collimators of the dimensions 3 mm × 25 mm. d is a collimator of the diameter 3 mm. D is the Ge-detector. O is the scatterer. The drawing is made almost on a correct scale. It is apparent from this that the chamber can easily be used on place in most existing x-ray equipments. The material of the filament is polyethylene, lucite or another material of a low average atomic number providing rapid and precise reconstructions. In the example shown air scattering corresponds to a very small portion of the totally detected intensity. In the practical embodiment of the invention our calculation algorithms are preferably implemented in a computer so that a handy measuring instrument is obtained.

Claims: 1. A method for measuring high energy electromagnetic radiation by means of scattering where the high energy radiation and the spectrum of the scattered radiation is measured (8) at an angle to the original beam path and that thereafter the original spectrum is reconstructed from the measured spectrum, characterized in that a scatterer is used that is in the form of a long and narrow filament (4) or a long and narrow rod placed in the beam path of the high energy radiation that is to be measured. 2. A device for carrying out the method of claim 1 comprising a chamber having an aperture for the incident electromagnetic radiation, a scattering element provided in the chamber and a detector arranged at an angle relative the entering beam path of the high energy radiation that is to be measured characterized in that the scattering element is in the form of a long and narrow filament (4) or a long and narrow rod. 3. The device of claim 2, characterized in that the rod or filament is made of polyethylene, lucite or another material having a low average atomic number. 4. The device of any one of claims 2 or 3, characterized in that the detector angle is 90° relative to the incoming beam passage. 5. The device of any one of claims 2-4, characterized in that the filament or the rod has a circular cross-sectional area.

Inventors: MATSCHEKO, GEORG, RIBBERFORS, ROLAND
Applicants: MATSCHEKO, GEORG, RIBBERFORS, ROLAND
Application year: 1988
Main classification: G01T1
IPC codes: G01T1