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Zhutyaev, S. G.; Smelik, G. I.; Mishkinis, A. B.; Mishkinis, B. Ya.; Chikirdin, É. G.

doi:10.1023/a:1013735512822

Biomedical Engineering

2001

DOI: 10.1023/a:1013735512822

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S. G. Zhutyaev¹,

G. I. Smelik²,

A. B. Mishkinis³

et al.

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“…The X ray tube anode in this case is made of tungsten (Z = 79). This equation takes into account attenuation in the filter [4]: …”

mentioning

confidence: 99%

Determination of the Practical Peak Voltage from the Bremsstrahlung Damping Rate in a Semiconductor Detector

Muslimov

Lelyukhin

2012

Biomed Eng

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The spectrum of the bremsstrahlung depends on X ray anode tube voltage, anode voltage curve, anode mate rial, anode slope angle, and equivalent total filtration rate. A new standard of X ray dosimeters is based on non invasive monitoring of X ray tube voltage with detection of practical peak voltage (PPV) [1]. According to the standard, PPV is determined as the constant potential providing the same contrast of air kerma behind the phantom as the voltage under monitoring.In practice, X ray tube anode voltage is measured using two or more PPV detection channels. Such chan nels have different spectral sensitivities. Air kerma asso ciated methods of PPV measurement are rather sophisti cated and can be implemented only in the laboratory.Determination of actual peak voltage from recovered spectral distribution of bremsstrahlung is described in this work. The bremsstrahlung spectrum is restored from absorption curves detected using a linear discrete semi conductor detector. The PPV value is calculated from the calibration curve.The absorption curve was plotted using a linear dis crete semiconductor detector in which the detection channels also provide a filtration function (Fig. 1).In the photon count mode of the detector, the absorp tion curve is a hyperbola with three segments: quasi linear attenuation segment determined by low energy photons; saddle segment determined by radiation rigidity; below saddle segment with constant radiation energy [2].The family of the absorption curves detected using the gallium arsenide detector is shown in Fig. 2. The abscissa is channel number and the ordinate is logarithm of brightness signal in each detection channel.If the abscissa is the product of linear density of detector material ρ·d (g/cm 2 ) multiplied by detector channel number i, the dimension of the absorption curve slope coefficient is the dimension of the mass extinction coefficient (cm 2 /g). The absorption curve shape is deter mined by the spectrum of the incident radiation.Approximation of this absorption curve is imple mented within the initial segment.The mathematical model of bremsstrahlung damp ing rate was constructed. This model was implemented for MathCAD software. The effect of anode voltage pul sation on test results was measured.Cramer's equation describes the X ray tube bremsstrahlung spectrum. The X ray tube anode in this case is made of tungsten (Z = 79). This equation takes into account attenuation in the filter [4]:Determination of the practical peak voltage from the bremsstrahlung damping rate in a linear discrete semicon ductor detector is described. The method of formation of absorption curves is given. Results of mathematical modeling of an absorption kilovoltmeter are presented. Fig. 1. Absorption curve formation scheme. Filter Emitter Detection channel Detector

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“…The X ray tube anode in this case is made of tungsten (Z = 79). This equation takes into account attenuation in the filter [4]: …”

mentioning

confidence: 99%

Determination of the Practical Peak Voltage from the Bremsstrahlung Damping Rate in a Semiconductor Detector

Muslimov

Lelyukhin

2012

Biomed Eng

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“…This method is based on calculation of spectral density of X ray radiation intensity, i.e., dependence of radiation intensity on quantum energy [13]. In contrast to conven tional methods of calculation of radiation intensity [5], the method suggested in this work has a number of specif ic features. First, it takes into account changes in spectral distribution in different media using a continuous rather than a discrete approach; second, it takes into account characteristic radiation of the X ray tube (contribution up to 1/3 total radiation intensity).…”

mentioning

confidence: 99%

Specific Features of High-Voltage Microfocal Medical X-Ray Diagnosis

Потрахов¹,

Gryaznov²

2005

Biomed Eng

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X Ray sources with focal spot size of less than 0.1 mm called microfocal X ray radiation sources (MXRS) are widely used in domestic medical practice of X ray diagnosis [6]. Efforts of domestic researchers are focused mainly on microfocal medical X ray diagnosis for injuries and diseases of the locomotor apparatus [3].It has been shown in recent years that microfocal medical X ray diagnosis in combination with digital tech nologies provides a promising approach to microsurgery of bone tissues [4]. As a result, microfocal medical X ray diagnostic apparatuses are widely used in dentistry, max illofacial surgery, rheumatology, traumatology, orthope dics, prosthetics, medical expertise, etc.In recent years MXRS models for voltages 50, 70, 100, 120, and 150 kV, and X ray diagnostic apparatuses on their basis have been developed and manufactured in Russia [7]. The power of such apparatuses is 10 30 W. The exposure dose of such apparatuses is low.Although microfocal roentgenography provides high quality X ray images, specific features noted above impose restriction on the use of MXRS [11].X Ray photography at enhanced anode voltage is an approach to elimination of the disadvantages of microfo cal medical X ray diagnostic apparatuses.It was shown in [6] that correlation between X ray radiation intensity, anode voltage, anode current, and dis tance to the point of measurement (focal distance) is described by the following semiempirical equation:where J is the X ray radiation intensity; k is a scaling fac tor; i A is the anode current; Z M is the atomic number of the target material; U is the anode voltage, n = 2 5 depending on thickness and density of object; R is the focal distance. It follows from Eq. (1) that X ray radiation intensity at invariable anode current can be increased by decreas ing focal distance. Normalized data on the dependence of X ray radiation intensity on anode voltage calculated from Eq. (1) are given in Tables 1 4. The data were normalized to radiation intensity J 0 at standard conditions of X raying [8]: anode voltage, 100 kV; anode current, 50 mA; focal distance, 1000 mm. The calculations were performed for two factors n and two focal distances R.This distance 300 mm was chosen for the following reasons. At focal spot size 0.1 mm allowable image blur of

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Cited by 2 publications

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Determination of the Practical Peak Voltage from the Bremsstrahlung Damping Rate in a Semiconductor Detector

Determination of the Practical Peak Voltage from the Bremsstrahlung Damping Rate in a Semiconductor Detector

Specific Features of High-Voltage Microfocal Medical X-Ray Diagnosis

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