COLLIMATION OF X-RAY DIAGNOSTIC BUNDLE BY MEANS OF

STEERING FERROFLUID

Andrzej Dyszkiewicz

1,2,3

, Paweł Połe´c

1,3

, Jakub Zajdel

1,3

, Bartłomiej Pawlus

Damian Chachulski

1,3

and Paweł Kpi´nski

1,3

Laboratory of Biotechnology Cieszyn ul.Go´zdzik´ow, 2, Poland

Technical University of Opole, Faculty of Physical Education and Physiotherapy, Poland

Specialist Rehabilitation Department ”VIS” Cieszyn ul. Bielska 3A, Poland

Keywords:

Incoherence x-ray beam, Collimation of x-ray beam, Ferroﬂuids, Computer steering.

Abstract:

The study addressed the problem of the incoherence of an X-ray tube generated bundle. In spite of the large

progress made in the area of the durability and efﬁciency of these devices, the problem of the inherent diver-

gence of the bundle hasnt yet been resolved in a satisfying way. In the face of difﬁculties with concentrating

X-rays, the only practical way of eliminating non-axial rays is by applying lead collimators of a suitable length

and diameter as well as mechanical systems of movable distracting grids. An entirely new approach has been

the use of electro-magnetorheological ﬂuids as ﬁlters, which are capable of modifying their physical and quan-

tum properties contingently based on the parameters of the applied external electric current, centrifugal force

and magnetic ﬁeld. The experiments carried out showed, that the described changes also concern the absorb-

tion, distraction or change in the direction of the X-ray beam. In the constructed prototype device, interesting

and recurrent results in the modiﬁcation or eleimination of non-axial rays were obtained, which resulted in the

improvement of the quality of bone images. The following research questions were posed: (1) are changes

in the photodensitometric parameters of joint (PIP) X-ray images containing soft and osseous tissues proof

of alterations of the physical parameters of a diagnostic X-ray beam? (2) is there a relationship between the

volume of ferroﬂuid in a lens and its capability to alter the parameters of a permeating X-ray beam? (3) is there

a relationship between the r.p.m. of the collimator and its capability to alter the parameters of a permeating

X-ray beam, and does it have a linear character? Based on the conducted research a non-linear dependancy

was observed between the volume of ferroﬂuid in the lens as well as its rotational speed and the capability of

the system to alter the parameters of the permeating X-ray beam.

1 INTRODUCTION

William Roentgens pioneer works began a completely

new chapter in the history of medical diagnostics, en-

abling small invasive investigationsof internal organs,

especially the osseous tissue. Progress in the ﬁeld

of electronics resulted in X-ray tubes becoming in-

creasingly more efﬁcient, reliable and the repeatabil-

ity of emission in relation to a given electric param-

eter was largely improved (Bankier et al., Carlson,

Dyszkiewics, 2001, Dyszkiewics, Folster, Grampp et

al., 1997b, Ławniczak and Milecki, 1999). From

the dawn of the development of radio-photographic

technology, beginning with tubes with a motionless,

and later rotating and multi-focal anode, constructors

struggled with the problem of the originally divergent

diagnostic bundle, the geometry of which results from

the way an X-ray beam is formed as a consequence

of breaking the stream of accelerated electrons on the

anode. A divergent bundle produces geometrical dis-

tortions and leads to a considerable worsening of the

acutance of the photo. A large quantity of non-axial

rays is the reason for this phenomenon. Constructors

of X-ray tubes have been trying to achieve a larger co-

herence of the bundle for many years. As a result, the

use of collimators began, that is, thick-walled tunnels,

made of materials of a large thickness, able to absorb

non-axial rays. Applying tubes with a multi-focal

anode was another solution, which enabled a better

adaptation of the bundle geometry to the distance of

a photographed object. Still another solution was the

use of stable ﬁlters or oscillating metal grates placed

above the ﬁlm, distracting non-axial rays (Czerny et

al., 1997, Grampp et al., 1997a, Kainberger, et al.,

1997, Kollmann, et al., 1997, Kramer et al., 1997). In

spite of the results achieved in improving the quality

of X-ray images, it can be clearly observed that these

activities lead exclusively to the removal of part of the

441

Dyszkiewicz A., Połe

c P., Zajdel J., Pawlus B., Chachulski D. and Kpi

nski P. (2009).

COLLIMATION OF X-RAY DIAGNOSTIC BUNDLE BY MEANS OF STEERING FERROFLUID.

In Proceedings of the International Conference on Biomedical Electronics and Devices, pages 441-447

DOI: 10.5220/0001817704410447

 SciTePress

rays from the bundle by using materials of large den-

sity, which only increase the difference between the

real and effective power of the tube and have a mea-

surable inﬂuence on the weight and durability of the

device (Dyszkiewicz, 1999, Dyszkiewicz, 2001, Ma-

jumdar et al., 1997, Phule, Rand et al., 1997, Sasaki).

One new innovative solution used by scientists in

Geneva has been the application of ferroﬂuids with

variable physical and chemical parameters, which, af-

ter being introduced into capillary tubes placed in an

X-ray beam axis allow the parameters of the beam to

be changed contingently.

1.1 Ferroﬂuids

Ferroﬂuids display the characteristics of both ﬂuids

and magnetic substances at a very wide temperature

range. With the absence of an external magnetic

ﬁeld they behave like normal newtonian ﬂuids, where

the shear stress is in direct proportion to the shear

velocity without displaying any signs of magnetisa-

tion. The viscosity of controlled ferroﬂuids can be

adapted within a range of 5 - 25 000 cP. Analogi-

cally to electrorheological ﬂuids they are built of two

basic components: carrier ﬂuid (<85% ) and ferro-

magnetic particles covered with a surface layer (from

2% to 15% , for ferroﬂuids, up to 80% for MRF).

The carrier ﬂuid is a non-magnetic substance; how-

ever the components of the particles of the suspen-

sion are solid soft magnetic materials which form mi-

cromagnets [27]. Removing the action of Van der

Waals forces and magnetic attraction forces (group-

ing) makes it possible to cover the particles with a

surface active agent (e.g. oleic acid). Depending on

the size of the particles two types of ferroﬂuids can

be distinguished: (1) nanomagnetorheological also

called ferromagnetic; (2) magnetorheological ﬂuids

MRF. In ferromagnetic ﬂuids the diameter of the par-

ticles (most commonly Fe

) ranges from 3 15nm.

At smaller sizes they do not display any magnetic

properties. Normally, synthetic oil is used as a car-

rier, or (not so often) light mineral oil, esters, glycer-

ine, poliphenyl or water. The maximum magnetisa-

tion of 0,6T domains limits the magnetic absorption

of the ﬂuids (0,005 0,13 T) and the maximum shear

stress is less than 5 kPa. They can operate at tem-

peratures from -65 to 200 C, as it is within this range

that magnetisation is independent from temperature.

Their durability depends on the evaporative power of

the carrier ﬂuid, which should be as low as possible

whilst the conductivity of the entire system should

be the highest. As the particles are of small dimen-

sions they do not accumulate at the bottom of the

container even if the ﬂuid remains still for long pe-

riods of time (they are raised as a result of thermic

motions). In magnetorheological ﬂuids the size of the

particles ranges from 0,5 to 8 mm. Mineral or sil-

icon oil with a low evaporative power is used most

often as the carrier ﬂuid. In industrial applications the

magnetic induction can total 1,2T (max.2,15T).These

properties do not change within the temperature range

of -50 ÷ 150C. The maximum shear stress at a mag-

netic ﬁeld strength of 150 ÷ 250 kA/m is 50 to 250

kPa. A characteristic feature of magnetorheological

ﬂuids is their capability of rapidly (<10ms) changing

their viscosity after a relatively weak magnetic force

is applied. Leaving the magnetorheological ﬂuid still

leads to the accumulation of particles at the bottom of

the container, which is their drawback. However, their

production is much easier, making them signiﬁcantly

cheaper compared to ferromagnetic liquids. In the sit-

uation when an external magnetic ﬁeld is not present,

the magnetic moments linked to the particles are dis-

tributed at random, which leads to a complete dissipa-

tion of their forces. After applying an external force,

the magnetic moments of the particular particles line

up along the ﬂux created by the force ﬁeld and thus

are no longer subject to thermal currents. This mech-

anism is similar to the mechanism of chain creation

in electrorheological ﬂuids. Magnetorhelogical ﬂuids

display considerably stronger magnetisation than fer-

rorheological ﬂuids. By controlling the strength of

the magnetic ﬁeld we can inﬂuence the viscosity of

the ﬂuid, e.g. with a ﬁeld of ca. 200 kA/m it can

reach a value of 700 P for magnetorheological ﬂuids

and 50 P for ferromagnetic ﬂuids, which allows for

the application of shear stress of 100 kPa and 5 kPa

respectively.

1.2 New Methodology

The prototype device has been shown in ﬁg. 1a. It

consists of a ring with grooves adapted to the dimen-

sions of the electromagnets or solid magnets active

elements, which are synchronised geometrically and

parametrically to work at a desired angle within the

ring, where a suitable container with ferroﬂuid has

been placed.

1.3 Collimator Function

A collimator (ﬁg. 1a) is composed of a cylinder ﬁlled

with ferroﬂuid which serves as a diffraction crystal.

The ferroﬂuid, being situated inside a ring contain-

ing several or more powerful magnets with alternate

or compatible polarities becomes spatially organised,

forming the shape of a convex lens with a relatively

large curvature and containing additional smaller lo-

BIODEVICES 2009 - International Conference on Biomedical Electronics and Devices

442

Figure 1: Collimator for modifying the geometry and en-

ergy of the diagnostic X-ray radiation: (a) example arrange-

ment of ﬁxed magnets or electromagnets in induction ring;

(b) concept showing the relation between the induction of

the magnetic ﬁeld (increasing the thickness of the lens) and

centrifugal force in a rotating motion, the action of which

ﬂattens the curvature of the ferroﬂuid lense.

Figure 2: Collimation system: (a) view of ferroﬂuid inside

the inducting ring of the collimator at one magnet conﬁg-

uration; (b) laboratory unit on a adjustable stand equipped

with a dental X-ray tube.

cal convexes. After putting the entire arrangement

into motion by an electric motor, the action of cen-

trifugal forces which act in an opposite direction to

the magnetic inductance vector decrease the size of

the lens curvature proportionally to the speed with

which the magnetic ring turns and in inverted propor-

tion with the value of the magnetic inductance (ﬁg.

1b).

The X-rays emitted from the tube, when passing

through a collimator are curved to the axis, concen-

trated in the focal point or are diverged away from the

axis (dispersed) depending on the type of ferroﬂuid

used, the shape of the ﬁeld (depending on the num-

ber and induction of the used magnets or additional

electrodes) as well as on the rotational speed of the

collimator.This allows the rays which are outside the

axis to be aligned towards it or focused. Using a col-

limator also enables energetic ﬁltration to take place

which eliminates image distortions resulting from an

uneven distribution of radiation on the images plane

(initially divergent beam) (ﬁg. 2a).

The operation of the new generation collimator

Patent P366266 is based on Lawrence Braggs law,

which explains the mechanism of how the path of

hard radiation is distributed in a crystal. Ray 1 falls

Figure 3: The central element of the collimator is its rotat-

ing ferroﬂuid lens, the curvature of which is determined by

the relation between the centrifugal force and the magnetic

induction of the rings magnets. (a) the initially divergent X-

ray bundle is modiﬁed especially within the range of non-

axial beams (b) Braggs law describes this process.

onto the surface of the crystal at angle V and affects

the electron layer of atom C, whilst the second beam

which is parallel to beam 1 affects the layer of atom

M. The electron layers of the atoms scatter the X rays.

The symmetry straight AC which is perpendicular to

the incident rays constitutes the face of the incident

wave. Such is also line BC a wave scattered at an-

gle V. As a result the difference between the paths of

rays 1 and 2 is AM + MB. Triangle AMC produces

the following formula:

AM = dsinV(1)

where d is the distance between neighbouring planes

in the crystal. AM = MB, thus the difference between

the paths of beams 1 and 2 is:

2dsinV(2)

Ampliﬁcation takes place when the difference be-

tween the paths of two rays equals an integral mul-

tiple of the the length of wave 1. Thus the condition

for ampliﬁcation can be expressed by:

2dsinV = nl(n = 1, 2, ...)(3)

If this condition known as Braggs formula - is ful-

ﬁlled, then the scattered beams 1 and 2 become am-

pliﬁed and a reﬂection will occur. It can be noticed

that the reﬂection is a result of scattering and interfer-

ence (Bankier, et al.). Experiments have shown that

the computer controlled prototype collimator allows

a sharp focus of the divergent beam to be obtained in

a precisely determined point of a structure (ﬁg. 4a, b),

and the focus to be precisely moved within the tested

structure (scanning). Such a system creates the foun-

dations for gradient tomographywithout a need to use

the expensive gantry system and multislice scanners.

2 AIM OF WORK

The subject of the clinical tests was the RTG UDR1

prototype collimator. The tests were conducted

COLLIMATION OF X-RAY DIAGNOSTIC BUNDLE BY MEANS OF STEERING FERROFLUID

443

Figure 4: One of the ﬁrst images taken- the authors hand

showing two extreme parametrical compositions: (a) image

taken by axial beams at 770 r.p.m., displaying a sharp bone

trabeculae structure with an almost complete elimination of

soft tissue; (b) image taken with a non-axial beam com-

ponent at 650 r.p.m. displaying soft tissue with an almost

completely faded bone trabeculae structure.

among a group of healthy volunteers employed as re-

searchers at the Laboratory of Biotechnology. The

aim of the research was to answer the following ques-

tions:

(1) Does a ferroﬂuid which is spatially organised in

a magnetic ﬁeld and put into a spinning motion

change the properties of a permeating diagnostic

X-ray bundle produced by a dental X-ray unit?

(2) Are changes in the photodensitometric parame-

ters of joint (PIP) X-ray images containing soft

and osseous tissues proof of alterations of the

physical parameters of a diagnostic X-ray beam?

(3) Is there a relationship between the volume of fer-

roﬂuid in a lens and its capability to alter the pa-

rameters of a permeating X-ray beam?

(4) Is there a relationship between the r.p.m. of the

collimator and its capability to alter the parame-

ters of a permeating X-ray beam, and does it have

a linear character?

2.1 Subjects Tested and Method

Male white-collar volunteers aged 356, 7 , in good

health were qualiﬁed for the research.

Excluding Criteria. History of hand injury (bruises,

dislocation, fracture) treated by immobilisation, in-

ﬂammation of the joints, osteoporosis, diabetes,

heavy physical work or extreme sports, contact with

vibration, ionising radiation.

Testing Apparatus. The tests were carried out in a

standard room of the Laboratory of Biotechnology in

Cieszyn under the supervision of a Radiology Protec-

tion Inspector (of the Central Laboratory for Radio-

logical Protection), on a prototype UDR1 collimator

linked to a small-size Siemens X-ray unit for standard

dental diagnostics. All photos were made with a 0.5

second exposure time using 50kV to power the tube.

The registration of the bone structure radiograms and

their conversion to digital form was carried out on a

DIGORA dental 30 x 50mm matrix.

Test Method. The aim of the experiments was to test

the possibilities of controlling an X-ray beam by us-

ing different rotational speeds of a ferromagnetic lens

composed of different volumes of ferroﬂuid and also

to determine the applicability of the obtained photos,

which were modiﬁed in terms of quality, in diagnostic

medicine. The experiment schedule included:

1. Performing a series of shots of the PIP 3 (R) joint

with a lens containing 0.5 ml of ferroﬂuid at 11

ascending and repeatable rotational speeds of the

collimator.

2. Performing a series of shots of the PIP 3 (R) joint

with a lens containing 1.5 ml of ferroﬂuid at 11

ascending and repeatable rotational speeds of the

collimator.

3. Performing a selective densitometric analysis of

bone trabeculae groups in standard measurement

area locations (ﬁg. 5) by means of the Structure

1.0 software.

4. Performing an analysis in measurement areas lo-

cated diagonally to the length axis of the long

bone with visible soft tissue on one side of the

bone P(1) and on the other P(2) by means of

the authors trademark ”Density 1.0” software (ﬁg.

6,7).

Following a 5 minute acclimatisation in the labora-

tory, the tested persons were seated in a comfortable

position at station UDR1, placing their hands loosely

on the positioning pad. The trunk and legs of the pa-

tient were screened by a standard protective lead rub-

ber apron. The geometric axis of the lamp was di-

rected at the center of the picture converting matrix

size 20 x 30 mm, and the hand position pad forced

the third ﬁnger of the right hand to be situated so that

the axis also passed through the center of the PIP III

(R) gap. The distance between the bottom opening of

the X-ray tube collimator and the surface of the ma-

trix was 100mm. In the ﬁrst series the shot was taken

through a still lens containing 0.5 ml of ferroﬂuid.

Then the collimator was put into a spinning motion

for the 10 subsequent rotational speeds and shots were

taken at approx. 30-40 second intervals following the

stabilisation of the successively set speed. In the sec-

ond series the lens was replaced with one containing

1.5 ml of ferroﬂuid and all of the above procedures

were repeated for the 10 rotational speeds. A standard

system of DIGORA converting matrices was used to

be saved directly and repeatably in the computers op-

erational memory in BMP format which, as a result,

BIODEVICES 2009 - International Conference on Biomedical Electronics and Devices

444

Figure 5: ”Structure 1.0” graphical interface allowing for

the determination of the surface area of pixels belonging to

the visible bone trabeculae groups in measurement ﬁelds P

and D.

allowed for the complete elimination of errors which

could occur if the images were processed photochem-

ically.

X-ray Image Analysis

(1) Analysis of the visible bone trabeculae groups

surface area compared to the surface of the en-

tire image performed via the authors trademark

Structure 1.0 software implemented in the C++

environment. The standard area around the proxi-

mal phalangeal II (P) epiphysis and the distal pha-

langeal I (D) epiphysis, proximal interphalangeal

joint of the right hands third digit.

(2) Analysis of the X-ray shadows photdensitomet-

ric cross-section - was performed by the authors

trademark ”ensity 1.0” software implemented in

the ”Delphi 7.0 Professional” environment. The

program enables a photodensitometric evaluation

to be made of the image in the measurement ﬁeld

situated crosswise to the long bone axis with con-

sideration given to the soft tissue background on

one side of the bone (P1), the bone area (P3) and

the soft tissues (P2) on the other side of the bone

area (ﬁg. 5,6).

2.2 Results

Next pictures shows the results of photodensitometric

tests of bone trabeculae groups visible macroscopi-

cally in X-ray shadows of the PIP III joints, made in

a stand which positioned the axis of the bone against

the X-ray beam, and processed by the ”Structure 1.0”

software. The averaging results for the relative den-

sity in measurement ﬁeld P (proximal epiphysis) and

D (distal epiphysis) were based on the 11 tested col-

limator rotational speeds. The picture ﬁg. 8 presents

Figure 6: ”Density 1.0” graphical interface enabling the

preparation of a histogram displaying the optical density in

the measurement ﬁeld situated typically around the distal

phalangeal epiphysis of the right hand’s third digit. The

program performs a measurement in the soft tissue areas

P(1), P(2) and in the bone area.

Figure 7: Example histogram displaying the optical density

in area P(1), P(2), B(bone area).

differences between the average values in measure-

ment areas P and D.

Measurement data displayed in diagrams 8-10

show the non-linear dependency between the degree

of the modiﬁcation of the X-ray beam and the rota-

tional speed.

3 CONCLUSIONS

(1) The ferroﬂuid which has been spatially arranged

in a magnetic ﬁeld and put into a rotational motion

changes the properties of the permeating diagnos-

tic X-ray (with constant and repeatable parame-

ters), inducing changes in the clarity and optical

density of the soft tissue and bones.

(2) Changes in the optical clarity and translucency of

the analysed fragments of X-ray images of soft

tissues and bones obtained from a repeatable lamp

exposition at different collimator parameter set-

tings prove that changes in the physical properties

COLLIMATION OF X-RAY DIAGNOSTIC BUNDLE BY MEANS OF STEERING FERROFLUID

445

Figure 8: Averaging photodensitometric values of bone tra-

beculae groups in measurement areas P and D in X-ray

shadows made by the collimator at 11 rotational speeds of

the lens with ferroﬂuid (signiﬁcant changes occurred at 650,

770, 1000, 1350, 1450 r.p.m).

Figure 9: ”Structure 1.0” diagram presenting the averaging

optical density values of structures belonging to macroscop-

ically visible bone trabeculae in areas (P1) and (P2), (D1)

and (D2) for images made by lenses containing 0.5 and 1.5

ml of ferroﬂuid respectively.

of X-ray beams have occured

(3) A dependency has been noted between the vol-

ume of ferroﬂuid in the lens and its capability of

changing the permeating X-ray beam

(4) A non-linear dependency has been noted between

the rotational speed of the collimator and its capa-

bility of changing the permeating X-ray beam

4 DISCUSSION

The original divergence of a diagnostic X-ray bundle

resulting from the design of the X-ray tube is an is-

sue which has been accompanying radiological diag-

nostics ever since the emergence of the method. The

heterogeneity of the beam leads to signiﬁcant geomet-

rical changes of the image and causes an uneven dis-

tribution of radiation on the surface of the registering

matrix. Attempts at a compensating this issue focus

on two main areas:

(1) computer image processing

(2) technical elimination of non-axial beams

The collimation of non-axial diagnostic X-ray beams

has for long been performed by means of moving ﬁl-

ters (grids) or by lead collimators with thick walls

and a narrow pass which allowed only axial beams

to pass through. One drawback of using this type of

collimator is facing a signiﬁcant loss of the tube’s ef-

fective power as the axial beams constitute a small

share of the entire emission. Correcting an X-ray im-

age by homogenising the optical density and restoring

the geometric relations to a 1:1 status entail a com-

plete remodelling of the image matrix which results in

breaching the principle of ﬁling patients’ test results

in lossless formats (Dyszkiewicz, Wrbel; ICXOM

Vienna 2001). An interesting approach to solving

this issue were attempts at modifying the direction

of non-axial beams (Atkinson K, Folkard M et all;

ICXOM Chammonix 2003) based on magnetorheo-

logical ﬂuids which made it possible to make imme-

diate changes to the parameters of the beam by using

ﬁlters of varying densities (Remesh, N; Malagodi D at

all; ICXOM Chammonix 2003). A completely differ-

ent approach, on the other hand, was the idea of con-

structing a collimator which would be able to mod-

ify the propagation angle of non-axial beams towards

the axis and even to focus them (Dyszkiewicz, Wrbel

ICXOM Chammonix 2003), which would result in an

insigniﬁcant loss of energy from the initially diver-

gent beam while maintaining relatively good control

over the parameters of the produced image (e.g. expo-

sition of soft tissue (ﬁg. 4b) or hard tissue (ﬁg. 4a)).

The conducted laboratory experiments have proved

that the ferroﬂuid which has been spatially arranged

and put into motion by a magnetic ﬁeld changes the

properties of the permeating diagnostic X-ray beam

generated in a parametrically repeatable manner by

the tube (permanently coupled with the collimator),

located at a ﬁxed distance away from the tested dig-

its on the hand (positioned against the tubes axis by

means of a special stand), inducing changes in the

optical clarity and density of the contours of soft tis-

sue and bones. Changes in the contrast and thick-

ness of the edge contour of the bone tissue’s struc-

ture are accompanied by a change in the proportions

between the axial and non-axial rays in the diagnos-

tic beam, enabling or disabling the development of a

sharp and narrow border line in the presence of an

excess numer of rays. Changes in the optical clarity

and translucency of the analysed fragments of X-ray

images of soft tissues and bones obtained from a re-

BIODEVICES 2009 - International Conference on Biomedical Electronics and Devices

446

peatable exposition at a ﬁxed distance from the object

and different collimator parameter settings prove that

changes in the physical properties of X-ray beams oc-

cur. Proof of the existence of a dependency between

the volume of ferroﬂuid in the lens and the lens’ capa-

bility for modifying the parameters of the permeating

X-ray beam was of signiﬁcant importance in conﬁrm-

ing the inﬂuence of ferroﬂuid on the physical proper-

ties of an X-ray bundle. This may in the future lead

to the creation of lenses for various practical applica-

tions. A non-linear dependency has also been found

between the collimator’s rotational speed and its abil-

ity to modify the parameters of the permeating X-ray

beam. This feature seems to be best evidence that

interference occurs at closely quantized electron or-

bits of atoms belonging to the rotating quasi-crystal

of the ferroﬂuid as it should be remembered that if

the crystal was understood to operate as a simple stop,

the characteristics would most probably have a linear

character. Therefore the clear dependency between

the modifying properties of the collimator and the ro-

tational speed, exluding changes in the volume of fer-

roﬂuid, seems to be of signiﬁcant value for the fu-

ture perspective of creating easily-controllable units,

serially produced devices broadening the diagnostic

capabilities of standard X-ray tubes or enhancing the

further development of work on gradeint tomography.

Although the research results have been quite interest-

ing, it is important to bear in mind that the presented

scientiﬁc evidence concerning the modiﬁcation of an

X-ray bundle has an intermediate character, this due

to the fact that it deals with a secondary evaluation

of effects induced in the tested object following a

conversion of the ray’s energy into the visible light

range. The main reason why such an approach for

conducting this research was chosen is that the med-

ical community has become used to utilising X-ray

diagnostics in such a manner, as well as for its con-

siderably lower costs. Currently work is underway in

the Laboratory of Biotechnology on the next stage of

research which involves making direct measurements

of difraction and interference in the output X-ray bun-

dle after being modiﬁed by the collimator.

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