integrating additive manufacturing into the …...model output, i.e., compute a qualified guess of...
TRANSCRIPT
Page 1
THE WINSTON CHURCHILL MEMORIAL TRUST OF AUSTRALIA
Report by - CHRISTOPHER PAUL CARTY - 2017 Churchill Fellow
Integrating additive manufacturing into the treatment
pathway for children with bone deformities
Keywords
3D Printing
Additive Manufacturing
Surgery Planning
Orthopaedic Paediatrics
Deformity Correction
Patient Specific Surgical Guides
Musculoskeletal Modelling
Predictive Simulation
Page 2
31st August 2018
I understand that the Churchill Trust may publish this Report, either in hard copy or on the
internet or both, and consent to such publication.
I indemnify the Churchill Trust against any loss, costs or damages it may suffer arising out of
any claim or proceedings made against the Trust in respect of or arising out of the publication
of any Report submitted to the Trust and which the Trust places on a website for access over
the internet.
I also warrant that my Final Report is original and does not infringe the copyright of any
person, or contain anything which is, or the incorporation of which into the Final Report is,
actionable for defamation, a breach of any privacy law or obligation, breach of confidence,
contempt of court, passing-off or contravention of any other private right or of any law.
Christopher Paul Carty, PhD
Clinical Research Manager (Orthopaedics), Division of Surgery & Perioperative Services
Clinical Motion Analysis Consultant, Queensland Children’s Motion Analysis Service
Children’s Health Queensland Hospital & Health Service
Advance Queensland Fellow, Griffith University
Level 5, Centre for Children’s Health Research
62 Graham Street, South Brisbane Qld 4101
T: 3069 7194 ׀ F: 3069 7929 ׀ E: [email protected]
Page 3
Acknowledgements
I would like to thank the Winston Churchill Memorial Trust and Griffith University for the
ongoing support during my Churchill Fellowship. In particular, I would like to thank Professor
David Lloyd for his mentorship and his passion for disruptive technologies that will transform
the medical device industry, and Daniel Martinez-Marquez for sharing his extensive
knowledge on Quality by Design methodologies and collaborating with me during the
European phase of my travels. Furthermore, I would like to thank Martina Barzan (pictured
below left), Dr Sheanna Maine (pictured below right) and Dr David Bade for their continued
support on innovative projects that aim to improve surgery for children with bony
deformities. Finally, I would like to thank my wife Michelle and our four children Sophie,
Joshua, Isabella and Jessica for bravely supporting my absence during my travels and cheering
me up with video calls every evening from half way across the world.
Page 4
Executive Summary
The purpose of my Churchill Fellowship was to determine the potential for additive
manufacturing (i.e., 3D printing) to be integrated into the management pathway for children
with bony deformities. The great advantage of additive manufacturing is that is capable of
fabricating complex shapes, and manipulating material properties that are impossible with
traditional manufacturing methods and for these reasons show immense potential. The major
conclusions from my fellowship are as follows:
1. Equal time and effort should be invested in the quality processes that inform pre-
operative planning of surgery for complex lower limb deformities. More research on
advanced patient specific computational simulations is required to enable a more
objective surgical prescription process, and better understanding of actual loads
experienced by bones and implants during human movement.
2. The relationship between the orthopaedic surgeon and the design, or clinical, engineer is
crucial during the design phase of any custom 3D printed patient specific product. The
surgeon should be actively involved in the design phase of the product and be provided
an opportunity to gather hands on experience with any new surgical guide concepts.
3. Effective collaborative pre-planning and additive manufacturing will allow the surgeon to
execute the surgical plan in theatre in an accurate, precise and efficient manner.
Nonetheless, it recommended that more research be conducted on the efficacy of
patient specific surgical guides, as there remains a paucity of research in this area.
4. Industry and research institutions need to collaborate with regulatory authorities in the
near future to ensure product quality and safety, whilst not overburdening the quality
control process with redundant methodologies.
Page 5
Fellowship Programme
Dates Location Organisation Individuals visited
29th June – 5th July Leuven. Belgium Materialise Dr Sebastian De Boodt Dr Pieter Slagmolen Dr Sjoerd Kolk Dr Maria-Elvira Zeman Dr Roel Wirix- Speetjens Sharifah Fareena Aljunid
KU Leuven Professor Ilse Jonkers Professor Friedl De Groote Dr Hans Kainz Dr Hoa Hoang
5th July – 7th July Hamburg, Germany implantcast Marcus Junge Peter Scheinemann Klemens Terhaer Lia Schenk Gregor Besser
7th July – 14th July Dublin, Ireland World Congress of Biomechanics
Conference attendance
VU Amsterdam Prof Jaap Harlaar Dr Marjolein van der krogt
Imperial College London
Dr Luca Modenese
14th July – 22nd July Warsaw, USA OrthoPediatrics Dr Mallory Trusty Dr Peter Armstrong Joe Hauser David Daniels Fred Hite David Bailey
Zimmer Biomed Aaron Smits Josh Catanzarite Troy Hershberger
22nd July – 28th July Vancouver, Canada BC Children’s Hospital
Dr Emily Schaeffer Dr Liam Johnson Eva Habib
Centre for Hip Health and Mobility
Dr Sima Zakani Prof David Wilson
Page 6
Definition of terms
3D: Three-dimensional
4D: Four-dimensional
Accuracy: Accuracy is used to describe the closeness of a measurement to the true value (ISO 5725)
Additive Manufacturing: The process of joining materials to make objects from 3D model data,
usually layer upon layer, as opposed to subtractive manufacturing methodologies
Avascular necrosis: The death of bone tissue due to a lack of blood supply
Biomechanics: The study of the mechanical laws relating to the movement or structure of
living organisms
Bone implant: Use of natural or artificial materials for osseous reconstruction
Bony scaffold: A medical process used to regrow bone tissue. Damaged cells grip to the scaffold and
begin to rebuild missing bone and tissue through tiny holes in the scaffold
CAD: Computer-aided design. The use of computer systems to aid in the creation, modification,
analysis, or optimization of a design
Cerebral Palsy: A condition marked by impaired muscle coordination and bony deformity resulting
from damage to the brain before or at birth
CT: Computed tomography. The CT scan can reveal anatomic details of internal organs that cannot
be seen in conventional X-rays
Digital twin: A digital replica of physical assets (physical twin), processes and systems that can be
used for various computational modelling purposes
FDA: Food and Drug Administration (USA)
Neuromusculoskeletal modelling: Modelling the movements produced by the muscular and skeletal
systems as controlled by the nervous system
Machine learning: A field of computer science that uses statistical techniques to give computer
systems the ability to "learn" with data, without being explicitly programmed
Page 7
Medical device: An instrument, apparatus, implement, machine, contrivance, implant, in vitro
reagent, or other similar or related article, including a component part, or accessory
MRI: Magnetic resonance imaging. A medical imaging technique that uses a magnetic field and radio
waves to create detailed images of organs and tissues
Osteotomy: The surgical cutting of a bone, especially to allow realignment.
PMI: Patient matched implant
Precision: The closeness of agreement among a set of results (ISO 5725)
Predictive simulation: In musculoskeletal modelling predictive simulations can be used to predict
model output, i.e., compute a qualified guess of future output values based on past observations of
system’s inputs and outputs
QbD: Quality by Design. The approach is composed of eight main steps that follow in
a systematic way they can provide a deep understanding of the product and its manufacturing
process, including the identification and control of all variables to ensure desired quality
Saw bone: An artificial bone produced for the practice surgical techniques
SCFE: Slipped capital femoral epiphysis. A medical term referring to a fracture through the growth
plate (physis), which results in slippage of the overlying end of the femur (metaphysis)
Selective laser sintering: An additive manufacturing technique that uses a laser as the power source
to sinter powdered material (typically nylon/polyamide), aiming the laser automatically at points in
space defined by a 3D model, binding the material together to create a solid structure
Surgical guide: A medical device that is 3D printed based on patient specific medical imaging. It is
used to accurately assist in placement of surgical tools or devices bone
TGA: Therapeutic Goods Administration (Australia)
Virtual Surgery: Computational technique of simulating surgery procedure, which help Surgeons
improve surgery plans and practice surgery process on 3D models
Page 8
Integrating additive manufacturing into the treatment
pathway for children with bone deformities
Background
Paediatric bone deformities can result from congenital conditions or acute injuries and often
require orthopaedic intervention. For example, a femoral de-rotation osteotomy can address
the in-toeing gait of a child with cerebral palsy [1], or correct the out-toeing gait subsequent
to a slipped capital femoral epiphysis fracture (SCFE) [2]. Corrective osteotomies for
paediatric bone deformities are highly complex and require meticulous surgical pre-planning
and precise surgical execution. There have been a number of procedures described to correct
proximal femoral geometry in children with deformity subsequent to SCFE [3], which can be
broadly classified by anatomical region including subcapital, base of the femoral neck or
intertrochanteric, with the latter being preferred due to reduced risk of avascular necrosis.
For this reason, the present report will focus on utilising additive manufacturing to assist with
an intertrochanteric osteotomy.
The typical patient management pathway for paediatric deformity correction is depicted in
figure 1. First, the patient presents to the orthopaedic surgeon for an initial consultation.
During the consultation, the surgeon will gather the patient’s medical history and will perform
a physical evaluation. When indicated, the surgeon will refer the patient for medical imaging
(x-ray, CT or MRI) to visualise the deformity and/or three dimensional (3D) gait analysis to
determine the consequence of the deformity on the patients walking gait. The results from
medical imaging and 3D gait analysis are viewed independently and interpreted by the
orthopaedic surgeon. Once the surgeon has determined the preferred intervention the
Page 9
surgery is planned from the static medical imaging and is executed in theatre. Depending on
the preference of the surgeon, they may mark the angle of the osteotomy wedge directly on
the bone or insert a guide wire at the desired angle. Following the osteotomy, the distal
segment is aligned and fixation is achieved using a dynamic compression plate, blade plate or
dynamic hip screw and plate device. Post-operatively patients are encouraged to participate
in a rehabilitation program and are evaluated for progress. At approximately 12 months post-
surgery medical imaging and/or 3D gait analysis is conducted to evaluate outcomes.
Figure 1. Typical patient management pathway for paediatric deformity correction
Additive manufacturing also known as 3D printing is an emerging manufacturing technology
in the biomedical field. The great advantage of this technology is that is capable of fabricating
complex shapes, and manipulating material properties that are impossible with traditional
manufacturing methods. The printers are supported by software to build three-dimensional
Surgeon consult
Medical imaging
+/- gait analysis
Surgery
planning
Surgical execution
Rehabilation
Page 10
physical models from a series of cross sections, which are automatically joined together to
create the final shape [4]. A number of different additive manufacturing methods are
currently being implemented in the biomedical field and include stereolithography, selective
laser sintering, Inkjet 3D printing, electron beam melting, polyjet photopolymer and fused
deposition [5, 6]. Furthermore, there are a variety of materials that can be used by these
additive manufacturing methods, which may include plastics, ceramics and metals [4, 7]. For
complex surgical procedures, such as the intertrochanteric osteotomy, there exists an
opportunity to use additive manufacturing technology to assist surgical planning (e.g. 3D
printed anatomical models), aid surgical guidance (e.g. patient specific cutting guides) and/or
develop custom surgical fixation devices (e.g. bone implants).
Custom 3D printed orthopaedic solutions for paediatric deformity correction, including bone
implants, scaffolds or surgical guides have to overcome several barriers from a quality control
perspective, Firstly, medical devices are strictly regulated by organizations such as FDA (USA),
EMA (European Union), and TGA (Australia), in order to ensure their compliance to medical
specifications and consistency in manufacturing practices. Moreover, current standardization
methods applied to traditional manufacturing methods are not suitable for 3D printing
technology [8]. As a result, there is a lack of standardization and defined quality control
processes. Furthermore, additive manufacturing incorporates new technologies in the
biomedical field, and the design and fabrication of custom medical devices requires many
steps that might lead to imperceptible errors, affecting the performance and consequently,
patient safety. Successful industry transformation to this new design and manufacturing
approach requires technology integration, concurrent multi-disciplinary collaboration, and a
robust quality management framework.
Page 11
Fellowship aims
To determine the potential for additive manufacturing to be integrated into the management
of children with bone deformities. Specifically, this report will investigate:
I. The potential of 4D medical image simulation for surgical-pre planning
II. The engineer to orthopaedic surgeon relationship
III. Additive manufacturing of patient specific cutting guides
IV. Quality assurance and regulatory approval
Page 12
The potential of four dimensional (4D) medical image simulation for
surgical-pre planning
During the second week of my fellowship, I attended the 8th World Congress of Biomechanics
in Dublin, Ireland. This congress represents the premier meeting worldwide in the field of
Biomechanics. In brief, biomechanics is the study of the mechanical laws relating to the
movement or structure of living organisms. Human research in this field sits at the interface
of engineering and medicine and has revolutionised medical device technologies. The World
Congress of Biomechanics was attended by over 3,000 delegates and comprised of 15 parallel
sessions for most timeslots across the conference programme. Consequently, I focussed my
attendance on advances in medical imaging, neuromusculoskeletal modelling, paediatric
biomechanics, cerebral palsy, predictive simulation and medical devices. A major theme that
emerged from the conference was the pursuit of a simulation framework to allow accurate
predictive modelling following surgical intervention (e.g. muscle lengthening, bone
osteotomy) or musculoskeletal adaptation (e.g. muscle strengthening, robotic devices). The
two research groups at the forefront of this pursuit were led by Professor Benjamin J Fregly
in the Department of Mechanical Engineering, Rice University, Houston, TX, USA, and,
Professors Ilsa Jonkers and Friedl De Groote in the Human Movement Biomechanics Research
Group, KU Leuven, Leuven, Belgium. Furthermore, I had the opportunity to meet with some
of my international collaborators to discuss the current state of technology in predictive
modelling. It was clear the advances in the field of biomechanics could be used to improve
the typical patient management pathway described in figure 1. Based on the many
presentations and discussions on this topic a new framework for objective surgical
prescription is proposed (see Figure 2).
Page 13
Figure 2. A new framework for objective surgical prescription and execution
Similar to the typical patient management pathway the patient presents to the orthopaedic
surgeon for an initial consultation, however, rather than an independent evaluation of
medical imaging and 3D gait analysis this data is merged to create a neuromuscuoskeletal
model, or ‘digital twin’. The digital twin is then calibrated to ensure that the simulation can
match the experimental data [9, 10]. The calibrated model can then be virtually adjusted (see
figure 3) and a predictive simulation could be used to determine the potential consequence
of the chosen surgical intervention. Virtual surgery planning is an innovative solution and will
allow the identification of the limitations, constraints, and risks of the surgery [11].
Furthermore, virtual planning improves technical performance, gives confidence, and pays
dividends on the day of the actual procedure [11]. Once an optimal surgical intervention is
determined, an appropriate implant can be selected from those available on the market, or
could be 3D printed. To assist the surgeon in executing in their pre-operative surgical plan,
patient specific surgical guides could also be 3D printed.
Page 14
Figure 3. Virtual surgical adjustment to simulate an osteotomy.
Following surgery, a rehabilitation program is provided to the patient, however, in this
framework the rehabilitation program is specifically targeted to the expected post-surgical
impairments as predicted by the simulation [12]. A targeted rehabilitation program could
particularly be helpful for children with limited capacity and/or energy in the months
following surgery (e.g. patients following bone tumour resection). Finally, at 12 months post-
surgery the patient is assessed with medical imaging and 3D gait analysis, but this time the
information is not lost, rather it feeds back into the workflow using machine-learning methods
[13], thereby enabling process to be adapted in future to reduce discrepancies.
In summary, advances in biomechanics will allow a more objective surgical prescription
process and 3D printing technology will play an important part in aiding the surgeon with
custom devices and also tools to executive the surgical plan. Nonetheless, it is important to
state that without an effective pre-operative surgical plan, 3D printed solutions will not
enhance surgical outcomes because the precise execution of a sub-optimal surgery will still
lead to suboptimal outcomes.
Page 15
The engineer to orthopaedic surgeon relationship
A common theme that emerged from discussions with orthopaedic companies who offered
patient specific solutions was the need for a strong collaborative relationship between the
orthopaedic surgeon and the design engineer. In this section, I will briefly describe the
collaborative engineer-surgeon process implemented by the companies that I visited.
Materialise
In Leuven, I met with the osteotomy team at
Materialise, headed by Maria-Elvira Zeman. Maria
took me through the history of the company’s
methods in collaborating with hospitals to provide
patient specific solutions for complex deformities.
In total, their team had provided virtual surgical
pre-planning and/or the manufacture of cutting
guides via 3D printing for over 2,000 cases, with
the demand growing each year. The portfolio
included deformity correction for upper and lower
limb deformities. In their workflow, the
orthopaedic surgeon sends medical images to
Materialise and a clinical engineer segments the
medical images and subsequently creates a preliminary virtual design for the deformity
correction. The proposed implant may be informed by the surgeon’s preference or might be
sourced from those available on the market. The preliminary design is presented to the
surgeon who subsequently makes suggestions based on clinical experience and the virtual
Page 16
plan is adjusted accordingly. Once the plan is decided, a single guide is manufactured from a
regulatory approved polyacetylene base powder with selective laser sintering. The guides are
typically produced with cutting slits for the wedge resection, drill holes for the guide wire
placement, and drill holes for pre-drilling of the tunnels for plate fixation. Furthermore,
should an appropriate corrective device not be available on the market the Materialise team
also has the capacity to 3D print their own custom fixation devices (see Figure 4).
Figure 4. Example 3D printed fixation devices at developed by the Materialise osteotomy team.
Zimmer Biomed
In Warsaw, “The Orthopaedic
Capital”, I met with the Patient
Matched Implants (PMI) team at
Zimmer Biomed comprising of
Aaron Smits (Technical Graphics
Manager, PMI), Josh Catanzarite
Page 17
(Engineering Manager, PMI), and Troy Hershberger (Director, PMI). The team informed me of
the two separate departments at Zimmer Biomed that use 3D printing in designing patient
specific solutions. The PMI department typically deals with lower incident unique cases where
standards products are not available and therefore patient matched solutions are requested.
Interestingly, the demand for the PMI service is growing and the team is expanding. An
example of a PMI request might be to provide a solution to reconstruct the hip at the pelvis
and femur subsequent to tumour resection. The other department focuses on production of
personalised surgical guides for mass produced knee, hip and shoulder implants. I was
particularly interested in discovering how the team conveys to the surgeon the benefit of
patient matched solutions. Together we agreed that evidence for the benefit of cutting
guides, for example, could be provided by citing research on the superior outcomes shown
for guides that are used in knee replacement surgery to restore the mechanical or anatomical
axis [14-17]. However, the evidence for the benefit of customised solutions for complex
deformity is less clear and not yet available in the literature, partially due to the difficulty in
designing such a study and longitudinally tracking economic benefits. To overcome this lack
of scientific evidence the team conducts hands on workshops with orthopaedic surgeons
using saw-bones. The team recently conducted a study with a group of surgeons where a
guide wire was to be inserted in the glenoid fossa and oriented towards a specific notch on
the scapula. This process was then repeated with the use of 3D printed surgical guides. Follow
up investigations with CT revealed the variability in guide wire placement using a manual
approach, whereas the guided approach was accurate, precise and efficient. The experiment
allowed the surgeons to visualise the benefit of the guides and they are now strong advocates
for the use of surgical guides in clinical practice.
Page 18
OrthoPediatrics
In Warsaw, I also met with
the team at OrthoPediatrics,
who are an orthopaedic
company solely focused on
products for the paediatric
orthopaedic market. The
founders of the company saw
that paediatric surgeons
were forced to modify adult size implants in the operating theatre to fit the implant to the
child. OrthoPediatrics was founded with the vision to address the problem of off-label use of
adult implants. The company now has an extensive number of products that are designed to
cater specifically for the paediatric patient. OrthoPediatrics are not currently producing
patient specific implants but do collaborate with an external company (MightyOak Medical -
https://mightyoakmedical.com/) who design surgical navigation guides for their spinal
deformity implants. I did not have the opportunity to visit the team at Mighty Oak medical in
Denver, Colorado, but was able to connect with the President of the company and the Chief
Operating Officer via a phone interview prior to my departure. The company echoed the need
for a close relationship between the design engineer and the surgeon. They also shared
feedback from paediatric spinal surgeons who reported that the surgical navigation guides
were particularly helpful when performing complex scoliosis surgeries in paediatric patients.
Page 19
Implantcast
In Hamburg, I met with the team at Implantcast who also had a well-established process for
digital, pre-operative planning, which was similar to the process implemented at Materialise
and can be reviewed in detail at the following website (https://www.implantcast.de/en/for-
medical-professionals/products/individual-prosthetics/c-fitr-3d/). Implandcast produces
approximately 10
patient-specific implants
per week with a total of
500 implants per year. I
had the opportunity to
sit down with design
engineers Lia Schenk
and Gregor Besser and
was able to ask a
number of questions related to medical imaging segmentation and the virtual surgery design
process. Furthermore, I had a hands-on experience on a number of de-identified patient case
studies whereby segmentation and virtual design of surgery was conducted. The complexity
of each case highlighted the difficulty confronted by many orthopaedic surgeons in planning
and executing surgery for complex deformities. Furthermore, the precision required by Lia
and Gregor to segment the images and create a virtual plan underlined their high level of
specialised skill in design engineering and the important role they play in treating the patient.
The case studies highlighted the potential of additive manufacturing for virtual surgery,
surgical guides and metal implants and covered many body regions including pelvis, distal
tibia / calcaneus, distal radius, proximal radius / ulna, shoulder /scapula and femur.
Page 20
Summary
In summary, the relationship between design, or clinical, engineer and the orthopaedic
surgeon is crucial during the design phase of any patient specific product. Providing an
opportunity for the surgeons to test any surgical guides on saw bones, and/or providing 3D
printed models of the deformity aids the surgeon in planning complex deformity corrective
surgeries. The combination of effective collaborative pre-planning and additive
manufacturing allows the surgeon to execute the surgical plan in theatre in an accurate,
precise and efficient manner. There appears to be a growing demand from orthopaedic
surgeons who would like to utilise custom patient specific solutions for their patients. In the
next section, I will discuss the design and additive manufacturing process of patient specific
surgical guides for an intertrochanteric osteotomy.
Page 21
Additive manufacturing of patient specific surgical guides
Following the collaborative development of a 3D virtual surgical plan, the surgeon may
request manufacture of patient specific instrumentation to accommodate accurate, precise
and efficient execution of the pre-operative plan in the operating theatre. The four companies
that I visited all had the capacity to provide 3D printed custom surgical guides to assist with
deformity corrective surgery. The guides were either designed and manufactured on site
(Materialise, implantcast), designed onsite with manufacturing outsourced (Zimmer Biomed)
or designed and manufactured via collaboration with external partners (OrthoPediatrics).
Should a hospital department buy a printer and print custom medical devices in a hospital?
A common misconception with 3D printing is that a hospital department can simply buy a 3D
printer and start printing custom medical devices. Although this may be partially true for
external devices (e.g. custom orthotics), it is certainly not recommended for custom medical
devices that are intended for use in an operating theatre. Indeed, medical device companies
are anticipating regulatory changes in the custom medical device market and consequently
are developing comprehensive quality control procedures. The workflow to produce a patient
specific surgical guide for a proximal femoral osteotomy using a blade plate can be
summarised as follows:
Segmentation of external femoral geometry from CT or MRI
Design of a base plate for the surgical guide considering the surgical approach and the
anatomy the will be exposed in surgery. In addition, the design for the inner surface
needs to allow intuitive and secure positioning to be achieved during surgery.
Page 22
Integration of the CAD model of the desired implant to determine the orientation of
the blade plate into the post-osteotomy proximal segment geometry, and the positon
of the fixation screws in post-osteotomy distal segment.
The outer surface of the base plate can then be designed to incorporate the
specifications of the medical tool dimensions and guide their orientation during
surgery. This includes the dimensions of the guide wires, drill bits, chisel and saw
blade.
Once the design of the medical tool placement is incorporated into the outer surface
of the base plate, labelling of hole/plane dimension should be incorporated into the
surface.
The final CAD model design of the surgical guide is then converted to an STL file for
printing. Note - prior to 3D printing any medical devices the manufacturer needs to
ensure validation of the print for all proposed print materials. This includes verification
of the external shape and verification that the material properties meet ISO standards
for all proposed print orientations.
During the initial prototyping stages, low quality materials and printers can be used to
create ‘proof of concept’ models. For example, Materialise used fused deposition
modelling for prototypes and functional testing.
Printing the surgical guide requires higher accuracy printing using materials that are
biocompatible with regulatory approval. Many of the companies use laser-sintering
technology and print with polyamide powder. In brief, the process produces 3D
printed parts by selectively fusing individual layers of powdered material using a laser.
Following the printing process, the powder bed and parts contained within are
allowed to cool before being removed from the build chamber. The 3D printed surgical
Page 23
guide needs to be extracted from the powder and all surface powder needs to be
removed.
Removal of the power is important given the intricate holes and slits that guide the
medical tools. The surfaces first need to be brushed, which removes the major part of
the powder, and then sandblasted to remove what the brush may have missed.
The part should have dimensional accuracy assessed and each guide hole/slit should
be inspected and trailed to ensure the intended medical tool fits into the respective
parts. Many companies will fulfil this requirement with manual measurement,
however optical and scanning probing systems are recommended because they
collect much more data in the same or less time, resulting in more correct handling of
geometrical imperfections [18]. These methods also allow a complete automation of
the measurements process [19], improve the representation of the real geometrical
feature, and provide a higher degree of flexibility in measurement settings [20].
The labelling of the guide also needs to be inspected for accuracy.
The guide then needs to be sterilised, labelled and packaged for patient use in theatre.
Summary
In summary, the process from design to manufacture of a surgical guide that can be used by
an orthopaedic surgeon in theatre is complex and requires specialised software, equipment,
and team of trained professional to ensure quality control at each step of the workflow
described above. In the next section, I will overview regulations regarding custom 3D printed
orthopaedics devices in the USA, Europe and Australia, and the quality control methods that
medical device companies are adopting to ensure they meet current regulatory requirement
and anticipate future requirement.
Page 24
Quality assurance and regulatory approval
The integration of 3D printed anatomical models, surgical guides and/or bony implants into
clinical practice in Australia will revolutionise the medical industry. However, this technology
introduces a new layer of complexity and variability in product characteristics and is currently
posing a serious challenge to regulatory bodies tasked with managing and assuring product
quality and safety. Traditional quality frameworks that have ensured the fabrication of
reliable medical devices in the past are limited to standardized manufacturing methods,
which base their quality control activities on lot sampling and statistical quality control
techniques. Such approaches are limited for customized products where the manufacturing
environment is reduced to a fraction of traditional manufacturing activities.
According to the Australian Therapeutic Good Administration (TGA), mass produced 3D
printed devices are governed by the same regulatory requirements as conventionally
manufactured devices. However, devices that meet the definition for ‘custom-made’,
whether 3D printed or otherwise manufactured, have different requirements and are exempt
from being included in the Australian Register of Therapeutic Goods (ARTG). They must
however, meet the requirements under the conformity assessment procedures for custom-
made medical devices specified in the regulations. At present, the TGA is considering changes
to current medical device regulatory frameworks for custom medical devices to mitigate risks
to patients, and to meet requirements for health care providers and manufacturers. In
November 2017, the TGA released a consultation paper proposing regulatory changes related
to personalised and 3D printed medical devices [21]. The consultation covered topics
including: new definitions for personalised devices, changes to the custom-made conformity
Page 25
assessment procedure, changes to the definition of manufacturer (including a potential
exception for health care practitioners and hospitals), a new classification for anatomical
models and digital 3D print files and regulating scaffolds that contain human origin material
under the devices framework rather than the biologicals framework. In May 2018, the TGA
released the feedback form the consultation process [22]. In general, the submissions from
industry, health care and government organisations indicated that there is still need for more
clarity. The need for clarification was especially evident regarding the boundary between the
proposed ‘custom-made’ and the proposed ‘patient-specific’ definitions. There were also
several submissions indicating uncertainty, and requesting further explanation of what
exactly would be seen as a medical device production system. Furthermore, the exemptions
for health care practitioners and hospitals were not fully supported, which fits well with above
recommendation regarding the difficulty of printing medical devices in a hospital facility with
hospital staff alone. There is still work to be done in Australia and the TGA is currently leading
an international harmonisation initiative for definitions for personalised medical devices
through chairing an International Medical Device Regulators Forum working group on this
topic.
During this transition phase, where regulatory bodies are updating procedures, the quality
assurance of custom 3D printed medical devices has been carried out in the medical device
industry without any specific standard for this technology [23]. Indeed, the companies that I
visited who used additive manufacturing conveyed that there was a lack of clarity in
regulatory requirements for 3D printed medical devices. Therefore, to ensure compliance
these companies follow the same regulatory requirements and submission expectations as
traditional manufactured medical devices. However, the sharing of quality control resources
Page 26
such as staff and technologies between the standard implants and the patient-specific
products can be counterproductive in the long term when the production of customised
products is increased. This strategy leads to the creation of more inspection activities that are
not necessarily required and/or appropriate for additive manufacturing, and these resources
could be better allocated to future innovative research and development activities. A
framework for quality control of 3D printed surgical guides is proposed below (see figure 5).
Currently I am working with Daniel Martinez Marquez, a colleague at Griffith University who
is working on a project investigating the use of the Quality by Design (QbD) system for custom
3D printed bone prostheses and scaffolds [24] with the aim of industry translation [25]. In
brief, the QbD system was created by the US Food and Drug Administration in 2004, which
aims to carefully design products, services and processes considering all aspects of their life
cycle [26]. The result is a flexible regulatory framework designed to improve pharmaceutical
manufacturing processes and enhance product quality [26]. QbD focuses on acquiring process
control through a deep understanding of products and processes using science, engineering
and quality risk management [27]. Moreover, QbD accelerates research timelines and reduces
development costs, by avoiding trial-and-error studies, and focusing on testing methods
towards product development [28-30]. As a result, the implementation of QbD can help to
reduce a regulatory burden that forces many product engineers to purposely design their
products to fit within existing approved thresholds in order to avoid seeking further time-
consuming approvals for minor variations [31].
Page 27
The purpose our current work is to develop a robust new design framework for the
development of custom 3D printed surgical guides, bone implants and scaffolds, through the
QbD approach, and using quality risk management tools to help industry and research to
optimize resources and accelerate product development time frames. Such adaptation of the
QbD approach should facilitate product understanding to support innovation and efficiency
by reducing of costs and waste. The next stage of this project is for Daniel to conduct follow
up interviews with the companies visited during my Churchill Fellowship in addition to other
world-leading orthopaedic manufacturing companies to develop a list of the most critical risks
on product quality, including preventive and corrective actions to mitigate these risks from
an industry and research perspective. The findings will be presented to the TGA.
Page 28
Figure 5. Workflow of additive manufacturing process for surgical cutting guides including main
quality control activities (adapted from [24])
Page 29
Recommendations and Conclusions
The purpose of my Churchill Fellowship was to determine the potential for additive
manufacturing to be integrated into the management of children with bone deformities.
1. Equal time and effort should be invested in the quality processes that inform pre-
operative planning of surgery for complex lower limb deformities. More research on
advanced patient specific computational simulations is required to enable a more
objective surgical prescription process, and better understanding of actual loads
experienced by bones and implants during human movement.
2. The relationship between the orthopaedic surgeon and the design, or clinical, engineer is
crucial during the design phase of any custom 3D printed patient specific product. The
surgeon should be actively involved in the design phase of the product and be provided
an opportunity to gather hands on experience with any new surgical guide concepts using
anatomical models, and if possible, patient-specific saw bones.
3. The combination of effective collaborative pre-planning and additive manufacturing will
allow the surgeon to execute the surgical plan in theatre in an accurate, precise and
efficient manner. Nonetheless, it recommended that more research be conducted on the
efficacy of patient specific surgical guides, as there remains a paucity of research in this
area.
4. Design to manufacture of a 3D printed surgical guide should be a collaborative process
and include a team of trained professional to ensure quality control. Industry and
research institutions need to collaborate with regulatory authorities in the near future to
ensure product quality and safety, whilst not overburdening the quality control process
with redundant methodologies.
Page 30
Future work and dissemination strategies
Since my return to Australia, I have engaged in follow up discussions with the companies I
visited during my fellowship, local Australian distributors of medical devices, university
researchers and medical professionals. I have also progressed a number of research projects
aimed at providing evidence for the application of 3D printing for medical devices in Australia.
Finally, I have been active in securing partnership funding to further research in this space.
Dissemination though presentation
I have been invited to provide presentations on my fellowship topics at the Queensland
Orthopaedic Physiotherapy Network conference on the 14th September 2018, the Australia and
New Zealand Paediatric Imaging conference on the 7th October 2018 and the Australian and
New Zealand Society of Biomechanics Conference on the 14th of December 2018. My colleagues
and I at Griffith University are assisting the Engineers Australia Biomedical College in developing
an event on the topic of 3D printing and the changes to the regulations of custom made medical
devices proposed by the TGA.
Research to address gaps in the literature
Prior to my Churchill Fellowship, I was successful in obtaining an Advance Queensland Mid-
Career Fellowship for the project ‘The Personalised Digital Patient: helping children with lower
limb deformities’. In brief, I will collaborate with an international medical device company,
Griffith University and Children's Health Queensland to apply digitally-enabled technology and
advanced manufacturing to create solutions for better health outcomes for children, and
generate commercial opportunities for the Australian medical device market. This project aims
Page 31
to address a number of the abovementioned recommendations. At present, the project has
ethical approval to be conducted as a clinical trial in the Lady Cilento Children’s Hospital,
Brisbane. The clinical trial is registered as a phase one clinical trial with the Australian and New
Zealand Clinical Trials Registry. A collaborative clinical trials research agreement has been
established between Griffith University (manufacture of cutting guides) and Children’s Health
Queensland Hospital and Health Service. Finally, manufacture and use of the custom medical
device (i.e., the patient specific cutting guides) in the clinical trial has been acknowledged by
the TGA according to the Clinical Trial Notification Scheme.
Partnership funding
In August 2018, I was part of a team of chief investigators from Melbourne University, Flinders
University and Griffith University who successfully obtained $4M funding from the Australian
Research Council to lead an Industrial Training Transformation Centre over the next four years.
This Centre, focused on Medical Implant Technologies, will train a new generation of
interdisciplinary engineers and transform the orthopaedic and maxillofacial implant industry in
Australia into international leaders. While meeting the research and development needs of
local companies, it will build strong networks with hospitals and international collaborations.
Industry benefits include informed industry standards, more support for clinical research and
expansion into new markets. Australians will have improved procedures and assessments for
more reliable surgery with safer and successful outcomes. Faster recoveries and higher patient
satisfaction will increase demand. Advances in materials and savings in time for procedures and
translation will reduce costs.
Page 32
Prototyping facility
My current and future projects will be facilitated by the support of Griffith University’s
Advanced Design and Prototyping Technologies Institute (ADaPT)
https://www.griffith.edu.au/advanced-design-prototyping-technologies-institute. ADaPT
brings together multi-disciplinary expertise across Griffith University in collaboration with
leading industry partners to push the boundaries in advanced design, prototyping and new
materials, in what is called the ‘next industrial revolution’ or Industry 4.0. Combining expertise
in micro and nano science, with big data analytics, artificial intelligence, complex medical
imaging and functional modelling and the latest in 3D printing and bioengineering, ADaPT will
be the flagship institute within the Gold Coast Health and Knowledge Precinct.
Page 33
References
1. Carty, C.P., et al., The effect of femoral derotation osteotomy on transverse plane hip
and pelvic kinematics in children with cerebral palsy: a systematic review and meta-
analysis. Gait Posture, 2014. 40(3): p. 333-40.
2. Caskey, P.M., et al., Gait outcomes of patients with severe slipped capital femoral
epiphysis after treatment by flexion-rotation osteotomy. J Pediatr Orthop, 2014. 34(7):
p. 668-73.
3. Abu Amara, S., J. Leroux, and J. Lechevallier, Surgery for slipped capital femoral
epiphysis in adolescents. Orthop Traumatol Surg Res, 2014. 100(1 Suppl): p. S157-67.
4. Prince, J.D., 3D Printing: An industrial revolution. Journal of Electronic Resources in
Medical Libraries, 2014. 11(1): p. 39-45.
5. Ho, C., et al., Laser resurfacing in pigmented skin. Dermatol Surg, 1995. 21(12): p.
1035-7.
6. Mazzoli, A., Selective laser sintering in biomedical engineering. Med Biol Eng Comput,
2013. 51(3): p. 245-56.
7. Bhatia, S.K. and S. Sharma, 3D-Printed prosthetics roll off the presses. Chemical
Engineering Progress, 2014. 110(5): p. 28-33.
8. Monzón, M., et al., Standardization in additive manufacturing: activities carried out by
international organizations and projects. Int. J. Adv. Manuf. Technol, 2015. 76(5-8): p.
1111-21.
9. Jackson, J.N., C.J. Hass, and B.J. Fregly, Development of a Subject-Specific Foot-Ground
Contact Model for Walking. J Biomech Eng, 2016. 138(9).
Page 34
10. Pizzolato, C., et al., CEINMS: A toolbox to investigate the influence of different neural
control solutions on the prediction of muscle excitation and joint moments during
dynamic motor tasks. J Biomech, 2015. 48(14): p. 3929-36.
11. Tetsworth, K., S. Block, and V. Glatt, Putting 3D modelling and 3D printing into
practice: virtual surgery and preoperative planning to reconstruct complex post-
traumatic skeletal deformities and defects. SICOT J, 2017. 3(16).
12. Jonkers, I., et al. Towards a simulation-based understanding of musculoskeletal
deformity and their therapeutic remediation in children with cerebral palsy. in 8th
World Congress of Biomechanics. 2018. Dublin, Ireland.
13. Fregly, B.J. Generating Subject-specific Predictions of Human Movement. in 8th World
Congress of Biomechanics. 2018. Dublin, Ireland.
14. Lombardi, A.V., Jr., K.R. Berend, and J.B. Adams, Patient-specific approach in total knee
arthroplasty. Orthopedics, 2008. 31(9): p. 927-30.
15. Ng, V.Y., et al., Comparison of custom to standard TKA instrumentation with computed
tomography. Knee Surg Sports Traumatol Arthrosc, 2014. 22(8): p. 1833-42.
16. Schotanus, M.G., B. Boonen, and N.P. Kort, Patient specific guides for total knee
arthroplasty are ready for primetime. World J Orthop, 2016. 7(1): p. 61-8.
17. Silva, A., R. Sampaio, and E. Pinto, Patient-specific instrumentation improves tibial
component rotation in TKA. Knee Surg Sports Traumatol Arthrosc, 2014. 22(3): p. 636-
42.
18. Liu, X., et al., Evaluation of uit on titanium alloy residual stress eliminating by ultrasonic
residual stress measurement system Rev. Adv. Mater. Sci, 2013. 33: p. 266-269.
19. Savio, E., L. De Chiffre, and R. Schmitt, Metrology of freeform shaped parts. CIRP
annals, 2007. 56(2): p. 810-835.
Page 35
20. Chen, F., G.M. Brown, and M. Song, Overview of 3-D shape measurement using optical
methods. Optical Engineering, 2000. 39(1): p. 10-23.
21. TGA, Consultation paper: Proposed regulatory changes related to personalised and 3D
printed medical devices, M.D. Brance, Editor. 2017.
22. TGA. Submissions received: Proposed regulatory changes related to personalised and
3D printed medical devices. 2018 [cited 2018 28/07/2018]; Available from:
https://www.tga.gov.au/node/842868.
23. Ituarte, I.F., et al., Additive manufacturing in production: a study case applying
technical requirements. Physics Procedia, 2015. 78: p. 357-366.
24. Martinez-Marquez, D., et al., Application of quality by design for 3D printed bone
prostheses and scaffolds. PLOS ONE, 2018. 13(4): p. e0195291.
25. Martinez-Marquez, D., et al. Quality by Design towards Standardization of 3D Printed
Bone Implants and scaffolds for Industry Translation. in 4th World Congress on
Electrical Engineering and Computer Systems and Sciences. 2018. Madrid, Spain.
26. Fahmy, R., et al., Quality by design I: application of failure mode effect analysis (FMEA)
and Plackett–Burman design of experiments in the identification of “main factors” in
the formulation and process design space for roller-compacted ciprofloxacin
hydrochloride immediate-release tablets. AAPS PharmSciTech, 2012. 13(4): p. 1243-
1254.
27. Vogt, F.G. and A.S. Kord, Development of quality‐by‐design analytical methods. Journal
of pharmaceutical sciences, 2011. 100(3): p. 797-812.
28. Krucoff, M.W., et al., Medical device innovation: prospective solutions for an
ecosystem in crisis. Adding a professional society perspective. JACC Cardiovascular
interventions 2012. 5(7): p. 790.
Page 36
29. Lawrence, X.Y., Pharmaceutical quality by design: product and process development,
understanding, and control. Pharmaceutical research, 2008. 25(4): p. 781-791.
30. Naidu, N.V.R., et al., Total quality management. Vol. 1. 2006, New Delhi: New Age
International (P) Ltd., Publishers.
31. Sangshetti, J.N., et al., Quality by design approach: Regulatory need. Arabian Journal
of Chemistry, 2014.